Function verification cartridge for use with device for the rapid detection of analytes

ABSTRACT

A system that rapidly detects the presence of a target analyte in a biological test sample, which includes a sensor for measuring a detectable signal generated upon the reaction of a biosensor reagent with a specific target analyte within the sample; a reservoir card that includes the biosensor reagent that further includes living, engineered biological cells, and wherein the reservoir card is configured to interface with a test cartridge base; a test cartridge base configured to accept the reservoir card and to be placed within the testing device, wherein the test cartridge base further includes a reaction chamber adapted to receive both the biosensor reagent and the sample and a fluid displacement mechanism that includes a dispensing plunger, wherein actuation of the dispensing plunger displaces the biosensor reagent in the reservoir into the reaction chamber where the biosensor reagent is mixed with the sample; and a function verification cartridge adapted to be received and recognized by the testing device, and that is operative to confirm the proper functioning of the plunger and the sensor.

BACKGROUND OF THE INVENTION

The described invention relates in general to systems, devices, and methods for detecting various analytes or other targets of interest in biological samples or other sample types, and more specifically to a biosensor-based system for detecting and identifying analytes of interest in real time based on the emission of a detectable signal when the biosensor reacts with a target or analyte of interest in a sample being tested.

In generic terms, a biosensor is a system or device used for the detection of a target or analyte that combines a sensitive biological component with a physicochemical detector component. The components of a typical biosensor system include a biological element, a transducer or detector element, and associated electronics or signal processors that display test results in a meaningful and useful manner. The biological element typically includes biological material such as tissue, microorganisms, organelles, cell receptors, enzymes, antibodies, nucleic acids, and the like that may be created by known biological engineering processes. The transducer or detector element works in a physicochemical manner (e.g., optical, piezoelectric, and/or electrochemical) that transforms the signal resulting from the interaction of the analyte with the biological element into another signal that can be more easily measured and quantified. Biosensors originated from the integration of molecular biology and information technology (e.g., microcircuits, optical fibers, etc.) to qualify or quantify biomolecule-analyte interactions such as antibody-antigen interactions. Considering that there is great demand for rapid, sensitive, easy-to-handle, and cost-effective detection tools for detecting infectious agents, pathogens or/and toxins in food (see, for example, Mead et al., Food Related Illness and Death in the United States, Emerging Infectious Diseases; Vol. 5, No. 5, September-October 1999 (607-625), which is incorporated by reference herein, in its entirety), there is an ongoing need for the utilization of biosensors in real-time, field-portable devices and instruments for the detection and identification of infectious agents, pathogenic microorganisms, toxins, and other contaminants in foods and many other items.

Previously, testing of samples for infectious agents was a time consuming and expensive process that was largely divorced from the manufacturing process. In order to test for the presence of an infectious agent, a sample was typically enriched or cultured. This process requires the presence of a lab, and typically, the involvement of scientists with expertise in performing the required test. Due to the need for additional culturing or enriching time, and specialized tools and skills, the testing could not easily be performed on-site during the manufacturing process. Consequently, the manufacturing process was typically divorced from the testing process, resulting in the need for costly recalls when the testing process later found the presence of infectious agents, and the like. In other settings, such as hospitals, delays in receiving test results for infectious agents can allow for the spread of such infectious agents.

Several proposals have been made to improve the speed of testing for infectious agents by using biosensors for detection. For example, application of the aequorin-Ca2+indicator to detect E. coli contamination in food products was reported by Todd H. Rider et al., A B Cell-Based Sensor for Rapid Identification of Pathogens, SCIENCE, 11 Jul. 2003, pp. 213-215, the entire disclosure of which is incorporated herein by reference. However, the Rider process suffers from several deficiencies, such as a low signal-to-noise ratio that makes the process unreliable for use in large-scale sample analysis.

Accordingly, it is desirable to provide a portable, self-contained system capable of rapidly testing samples for infectious agents or other targets in real time or near real time. It is further desirable to improve the technique of using biosensors for testing samples for infectious agents or other targets of interest by improving the signal-to-noise ratio that is an important aspect of such tests. It is further desirable to provide a testing device capable of being used by general staff for testing foodstuffs while in the manufacturing process. Finally, providing ongoing verification of the proper functioning of such a testing device is also a highly-desirable aspect of this technology.

SUMMARY OF THE INVENTION

The following provides a summary of certain exemplary embodiments of the present invention. This summary is not an extensive overview and is not intended to identify key or critical aspects or elements of the present invention or to delineate its scope.

In accordance with one aspect of the present invention, a first system for conducting an assay that rapidly detects the presence of a target analyte in a biological test sample is provided. This system includes a testing device, wherein the testing device includes a sensor for measuring a detectable signal that is generated upon the reaction of a biosensor reagent with a specific target analyte within a biological sample; a reservoir card, wherein the reservoir card includes a biosensor reagent, wherein the biosensor reagent includes living, engineered biological cells, and wherein the reservoir card is configured to interface with a test cartridge base; a test cartridge base, wherein the test cartridge base is configured to accept the reservoir card and to be placed within the testing device, wherein the test cartridge base further includes a reaction chamber that is adapted to receive both the biosensor reagent and the biological sample, and a fluid displacement mechanism that includes a dispensing plunger, and wherein actuation of the dispensing plunger displaces the biosensor reagent in the reservoir into the reaction chamber where the biosensor reagent is mixed with the biological sample; and a function verification cartridge adapted to be received and recognized by the testing device, wherein the function verification cartridge is operative to confirm the proper functioning of the plunger and the sensor prior to conducting an assay for rapidly detecting the presence of the target analyte in the biological sample, and wherein confirmation of proper functioning is based on predetermined operational parameters.

In accordance with another aspect of the present invention, a second system for conducting an assay that rapidly detects the presence of a target analyte in a biological sample is provided. This system includes a portable testing device, wherein the portable testing device includes a sensor for measuring a detectable light signal that is generated upon the reaction of a biosensor reagent with a specific target analyte within a biological sample; a reservoir card, wherein the reservoir card includes a biosensor reagent, wherein the biosensor reagent includes living, engineered biological cells, and wherein the reservoir card is configured to interface with a test cartridge base; a test cartridge base, wherein the test cartridge base is configured to accept the reservoir card and to be placed within the portable testing device, wherein the test cartridge base further includes a reaction chamber that is adapted to receive both the biosensor reagent and the biological sample, and a fluid displacement mechanism that includes a dispensing plunger, and wherein actuation of the dispensing plunger displaces the biosensor reagent in the reservoir into the reaction chamber where the biosensor reagent is mixed with the biological sample; and a function verification cartridge adapted to be received and recognized by the portable testing device, wherein the function verification cartridge is operative to determine displacement and travel speed of the dispensing plunger and functionality of the sensor prior to conducting an assay for rapidly detecting the presence of the target analyte in the biological sample.

In yet another aspect of this invention, a third system for conducting an assay that rapidly detects the presence of a target analyte in a biological sample is provided. This system includes a portable testing device, wherein the portable testing device includes a photomultiplier tube for measuring a detectable light signal that is generated upon the reaction of a biosensor reagent with a specific target analyte within a biological sample; a reservoir card, wherein the reservoir card includes a biosensor reagent, wherein the biosensor reagent includes living, engineered biological cells, and wherein the reservoir card is configured to interface with a test cartridge base; a test cartridge base, wherein the test cartridge base is configured to accept the reservoir card and to be placed within the portable testing device, wherein the test cartridge base further includes a reaction chamber that is adapted to receive both the biosensor reagent and the biological sample, and a fluid displacement mechanism that includes a dispensing plunger, and wherein actuation of the dispensing plunger displaces the biosensor reagent in the reservoir into the reaction chamber where the biosensor reagent is mixed with the biological sample; a function verification cartridge adapted to be received and recognized by the portable testing device, wherein the function verification cartridge is operative to determine displacement and travel speed of the dispensing plunger and functionality and sensitivity of the photomultiplier tube prior to conducting an assay for rapidly detecting the presence of the target analyte in the biological sample; and a heater for heating the reaction chamber, wherein the function verification cartridge is further operative to confirm proper functioning of the heater based on predetermined operational parameters.

Additional features and aspects of the present invention will become apparent to those of ordinary skill in the art upon reading and understanding the following detailed description of the exemplary embodiments. As will be appreciated by the skilled artisan, further embodiments of the invention are possible without departing from the scope and spirit of the invention. Accordingly, the drawings and associated descriptions are to be regarded as illustrative and not restrictive in nature.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated into and form a part of the specification, schematically illustrate one or more exemplary embodiments of the invention and, together with the general description given above and detailed description given below, serve to explain the principles of the invention, and wherein:

FIG. 1A is a rear perspective view of a testing device with a closed hinged lid for detecting infectious agents according to a preferred embodiment of the present invention;

FIG. 1B is a front perspective view of the testing device of FIG. 1A with the hinged lid open to show a cartridge recess;

FIG. 1C is a front perspective view of the testing device of FIGS. 1A and 1B showing a test cartridge inserted into the cartridge recess;

FIG. 2A is an exploded front perspective view of the components of an analysis portion of the testing device of FIG. 1 according to the preferred embodiment of the present invention;

FIG. 2B is a front perspective view of the analysis portion of the testing device of

FIG. 2A;

FIG. 3A is a front perspective view of a test cartridge assembly comprising a reservoir card inserted into a test cartridge base with a base lid closed for use with the testing device of FIG. 1 according to the preferred embodiment of the present invention;

FIG. 3B is a front perspective view of the test cartridge assembly of FIG. 3A with the test cartridge base lid open;

FIG. 3C is a bottom perspective view of the test cartridge assembly of FIGS. 3A and 3B;

FIG. 4A is a front perspective view of the test cartridge base with the base lid open of the test cartridge assembly of FIG. 3B according to the preferred embodiment of the present invention;

FIG. 4B is an exploded front perspective view of the components of the test cartridge base of FIG. 4A;

FIG. 5A is a front perspective view of the reservoir card in an initial arrangement for use in the test cartridge assembly of FIG. 3A according to the preferred embodiment of the present invention;

FIG. 5B is an exploded front perspective view of the components of the reservoir card of FIG. 5A;

FIG. 5C is a front perspective view of the reservoir card of FIG. 5A in an inserted arrangement to reveal fluid ports;

FIG. 6A is a magnified side view of a portion of the reservoir card in the initial arrangement of FIG. 5A with a folded-over film covering the fluid ports;

FIG. 6B is a magnified side view of the portion of the reservoir card in the inserted arrangement of FIG. 5C with the folded-over film retracted;

FIG. 7 is a magnified cross-sectional side view of a portion of the test cartridge assembly of FIG. 3A;

FIG. 8 is a cross-sectional side view of the test cartridge assembly of FIG. 3A;

FIG. 9 is a cross-sectional side view of the test cartridge assembly of FIG. 3A inserted into the analysis portion of the testing device of FIG. 2B;

FIG. 10A is a cross-sectional side view of the test cartridge assembly of FIG. 3A with a plunger in an initial position;

FIG. 10B is a cross-sectional side view of the test cartridge assembly of FIG. 3A with a plunger in a second position;

FIG. 10C is a cross-sectional side view of the test cartridge assembly of FIG. 3A with a plunger in a final position;

FIG. 11 is a schematic block diagram of the electrical components of the testing device of FIG. 1 according to the preferred embodiment of the present invention;

FIG. 12 is a schematic block diagram of a light sensing circuit of the testing device of FIG. 1 according to the preferred embodiment of the present invention;

FIGS. 13A and FIG. 13B are a flowchart of steps of a control application of the testing device of FIG. 1 according to the preferred embodiment of the present invention;

FIG. 14 is an exemplary graphical user interface of a home screen provided by the control application of FIGS. 13A and FIG. 13B;

FIG. 15 is an exemplary graphical user interface showing a test result provided by the control application of FIGS. 13A and 13B;

FIG. 16 is a flowchart of steps in which the test cartridge assembly 300 is utilized in conjunction with the testing device 100 for performing a test;

FIG. 17 is a chart illustrating the effectiveness of the system of the present invention with regard to detecting the presence of one or more infectious agents in a biological sample;

FIG. 18A is a perspective view of a function verification cartridge, in accordance with an exemplary embodiment of the present invention;

FIG. 18B is a top view of the function verification cartridge of FIG. 18A;

FIG. 18C is a bottom view of the function verification cartridge of FIG. 18A;

FIG. 18D is a front view of the function verification cartridge of FIG. 18A;

FIG. 18E is a side view of the function verification cartridge of FIG. 18A;

FIG. 18F is an exploded perspective view of the function verification cartridge of FIG. 18A;

FIG. 18G is a first cross-sectional view of the function verification cartridge of FIG. 18A (see top cross-section indicating arrow in FIG. 18C);

FIG. 18H is a second cross sectional view of the function verification cartridge of FIG. 18A (see bottom cross-section indicating arrow in FIG. 18C);

FIG. 19A is a top perspective view of the function verification cartridge of FIG. 18A positioned above the testing device of the present invention; and

FIG. 19B is a top perspective view of the function verification cartridge of FIG. 18A properly positioned within the testing device of the present invention.

FIG. 20 is a flowchart that illustrates the stepwise operation of a function verification cartridge from the perspective of the user of the disclosed system, in accordance with an exemplary embodiment of the present invention;

FIG. 21A and FIG. 21B are a flowchart that illustrates the stepwise operation of a function verification cartridge from the perspective of the function verification cartridge itself, in accordance with an exemplary embodiment of the present invention; and

FIG. 22A and FIG. 22B are a flowchart that illustrates the stepwise operation of a function verification cartridge from the perspective of the testing device (i.e., the PathOne' testing device), in accordance with an exemplary embodiment of the present invention.

DETAILED DESCRIPTION OF THE INVENTION

Exemplary embodiments of the present invention are now described with reference to the Figures. Reference numerals are used throughout the detailed description to refer to the various elements and structures. In other instances, well-known structures and devices are shown in block diagram form for purposes of simplifying the description. Although the following detailed description contains many specifics for the purposes of illustration, a person of ordinary skill in the art will appreciate that many variations and alterations to the following details are within the scope of the invention. Accordingly, the following embodiments of the invention are set forth without any loss of generality to, and without imposing limitations upon, the claimed invention.

Certain terminology is used in the following description for convenience only and is not limiting. The words “right,” “left,” “lower” and “upper” designate directions in the drawings to which reference is made. The words “inwardly” and “outwardly” refer to directions toward and away from, respectively, the geometric center of the stated component and designated parts thereof. Additionally, the words “a” and “an”, as used in the claims and in the corresponding portions of the specification, mean “at least one.” The terminology includes the words above specifically mentioned, derivatives thereof and words of similar import.

The present invention provides a portable, self-contained system for rapidly (i.e., within one to five minutes or more) detecting infectious agents, particularly pathogens in biological samples, particularly samples derived from beef, pork, or other meat, poultry, fish, or vegetable matter, although other biological materials, such as healthcare instruments and hospital surfaces, may be analyzed using the present invention. This system provides very high sensitivity (e.g., to a single cell of a particular infectious agent) without the need to culture infectious agents, such as bacteria, obtained from samples prior to testing. In an exemplary embodiment, the specific infectious agent is Escherichia coli, although other infectious agents (such as Salmonella, Listeria, and Campylobacter), toxins, and various contaminants may be detected with the present invention. Escherichia coli O157 H7, O26, O45, O103, O111, O121, and O145, in either separate assays or multiplexed assays, may all be detected using this invention.

Referring to the drawings in detail, wherein like reference numbers refer to like elements throughout the several figures, a portable, self-contained testing device 100 for performing a variety of real-time (or near real-time) qualitative tests to rapidly detect the presence of infectious agents in biological samples such as food and other substances is shown. Referring to FIGS. 1A-1C, the testing device 100 for performing a rapid (real time or near real time) analysis of a sample 414 (FIG. 4B) to identify infectious agents according to a preferred embodiment of the present invention is shown. In a preferred embodiment, the testing device 100 utilizes a disposable test cartridge assembly 300 to test for specific analytes in a qualitative manner. The testing device 100 is a portable analyzer that interacts with the test cartridge assembly 300 and provides simple prompts for a user to obtain results for specific tests that are designed to find offending analytes from a variety of sources. The test cartridge assembly 300, which interacts with the device, contains a living biosensor, which is engineered to detect and report an offending analyte in a sample 414. Samples 414 to be tested include materials such as food, liquids, surfaces, and the like which may be sources of infectious agents. Infectious agents include food borne illnesses, pathogens, viruses, bacteria, and the like. The testing device 100 allows for rapid analysis of the sample 414 to be performed without the time-consuming need to enrich or culture the materials being tested to facilitate the test.

FIG. 1A is a front perspective view of a testing device 100 with a closed hinged lid 104 in accordance with a preferred embodiment of the present invention. The testing device 100 includes an outer housing 102 which is preferably formed of a generally rigid, preferably polymeric material, such as acrylonitrile butadiene styrene. Other materials, or combinations of materials, may be used to form the outer housing 102 without departing from the scope of this disclosure. Such materials are well known to those skilled in the art.

The testing device 100 includes an ON/OFF power switch 108, and a touch screen liquid crystal display (“LCD”) 110 screen for permitting a user to interact with the testing device 100 when the power switch 108 is in the ON position. The touch screen LCD 110 allows the user to provide commands to the testing device 100, and provides instructions to the user by displaying menus to facilitate operation of the testing device 100, as shown in FIGS. 14 and 15. As will be discussed further, the menus include, but are not limited to, graphical user interfaces for providing information and/or data to the user concerning the status or results of a specific test or operation being performed by the testing device 100.

In a preferred embodiment, the touch screen LCD 110 comprises an LCD unit and an overlaid touch screen capable of receiving a user's input through a latex glove, or the like. In the present embodiment, the LCD 110 comprises a five (5) inch diagonal QVGA, IPS-based TFT LCD module VL-PS-COG-T500F2080-X1 from VARITRONIX, and a glass-film-glass resistive touch screen model AD-5.0-4RU-02-200 from AD METRO. Other models and manufacturers of the touch screen LCD 110 may be utilized without departing from the scope of this invention. Furthermore, other sizes and types of input/output devices, such as buttons, keyboards, track pads, and the like, may be employed in the testing device 100 without departing from the scope of this invention.

The testing device 100 includes a plurality of interface ports 112, such as an Ethernet port 112 a, and a micro USB port 112 b. The interface ports 112 allow the testing device 100 to interface, download, and upload data (e.g., test data), to or from a local or remotely located computing device, mobile device, server, or the like (not shown). The structure and operation of typical interface ports 112 are well known to those skilled in the art, and are not described in detail herein for the sake of brevity. While particular interface ports 112 have been described herein, other ports and other methods of wired and/or wireless communication, such as 802.11 Wi-Fi, may be integrated and utilized in the testing device 100 without departing from the scope of this invention.

Referring to FIG. 11, the external housing 102 of the testing device 100 also contains a power supply system 1126 and other electrical and electronic components, circuitry and software necessary to permit the testing device 100 to perform testing upon an installed test cartridge assembly 300. Preferably, the power supply system 1126 comprises one or more batteries 116 to facilitate stand-alone operation of the testing device 100. A battery charger connector 114 (FIG. 1A) is also provided to charge the one or more batteries 116, which are preferably rechargeable.

The one or more batteries 116 are each preferably comprised of a double-cell lithium ion battery, model 503759AY from AUTEC BATTERY, with 2200 mAh capacity at 3.7 volts nominally. The power supply system 1126 also includes an intelligent fast charge battery charging circuit 1114 which functions to recharge the batteries 116 and monitors the battery temperature using a temperature sensor embedded within the batteries 116. In the present embodiment, the battery charging circuit 1114 is a TEXAS INSTRUMENTS model BQ240032ARHLR. If the temperature of the batteries 116 is not within safe operating range, the battery charging circuit 1114 stops the charging of the batteries 116 until a safe temperature is reached. The battery charger is activated whenever an accompanying AC adapter (not shown) is connected to the testing device 100 through the battery charger connector 114 to provide power to the testing device 100 and permit normal use of the testing device 100 during the recharging of the batteries 116.

Referring to FIG. 1B, the testing device 100 of FIG. 1A is shown with its hinged lid 104 in an open position to reveal a cartridge recess 152. The cartridge recess 152 is preferably only accessible to a user when the hinged lid 104 is in the open position. As shown in FIG. 1A, the cartridge recess 152 is covered by the hinged lid 104 when the hinged line 104 is in its closed position. The hinged lid 104 is released by a mechanical actuator 106, preferably located on the outer housing 102, proximate to the hinged lid 104. The mechanical actuator 106, which is preferably a button, switch, or the like, releases the hinged lid 104 to rotate from the closed position, which is substantially integrated with the outer housing 102 as shown in FIG. 1A, to an open position, which is away from the outer housing 102, as shown in FIG. 1B. Referring to FIG. 1C, when the hinged lid 104 is in the open position, a test cartridge assembly 300 may be introduced into the cartridge recess 152.

As shown in FIGS. 1B and 1C, the hinged lid 104 contains two lid protrusions 104 a that are arranged to retain the hinged lid 104 in the closed position while a test is being performed by the testing device 100. In the closed position, the lid protrusions 104 a are engaged by a pair of locking latches 104 b contained within outer housing 102. The locking latches 104 b are disengaged from the lid protrusions 104 a by the user depressing the mechanical actuator 106. The hinged lid 104 preferably includes a light-sealing groove 118 having a light sealing gasket therein (not shown) which engages with a light sealing rib 120 in the analysis portion frame 202 (FIG. 2B) surrounding the cartridge recess 152 when the hinged lid 104 is in the closed position to prevent ambient light from entering the cartridge recess 152. A generally square projection 122 with tapered sidewalls on the interior surface of the hinged lid 104 engages with tapered sidewalls 204A of an analysis portion 200 housing 204 when the hinged lid 104 is in the closed position.

Referring now to FIGS. 2A and 2B, an analysis portion 200 of the testing device 100 according to the preferred embodiment of this invention is shown. The analysis portion 200 includes an analysis portion frame 202 that is contained within the outer housing 102. The analysis portion frame 202 is preferably arranged in a predetermined structure and orientation, having a first end 202 a and a second end 202 b to facilitate acceptance of a test cartridge assembly 300 (FIG. 1C), or other compatible testing container. An analysis portion housing 204, defining the cartridge recess 152, is positioned at a first end 202 a of the analysis portion frame 202. As shown in FIG. 1C, the cartridge recess 152 allows a user to introduce a test cartridge assembly 300 into the analysis portion 200 of the testing device 100 when the hinged lid 104 is in the open position. The analysis portion housing 204 functions as the interface between the testing device 100 and the test cartridge assembly 300. As will hereinafter become apparent, the disposable test cartridge assembly 300 is employed for collecting and introducing a test sample 414 (FIG. 4B) into the testing device 100 for the purpose of performing one or more tests on the test sample 414.

The analysis portion housing 204 of the analysis portion 200 will now be described in further detail. The analysis portion housing 204 is preferably made of a generally rigid, polymeric material such as acrylonitrile butadiene styrene or some other such polymeric material well known to those skilled in the art and is located within the analysis portion frame 202. The analysis portion frame 202 provides structural support to the analysis portion housing 204 and is the main component in a light sealing scheme which greatly minimizes or prevents ambient light from entering the cartridge recess 152 by way of the rectangular walls that surround the analysis portion frame 202, thereby preventing environmental light emissions from reaching a sensor 206. In a preferred embodiment, the sensor 206 is a light sensor.

The testing device 100 performs a desired test upon a sample 414 retrieved from a variety of sources by analyzing the electrical output of the sensor 206. When the sensor 206 is a light sensor, the output varies with the amount of light incident on the sensing surface 206 a of the light sensor 206 having originated within the test cartridge assembly 300. Based on the type of test being performed, the output of the light sensor 206 determines whether the analyzed sample 414 is positive or negative for the presence of the material (infectious agent) that is being sought in a qualitative analysis. That is, there need not be a determination by the testing device 100 of the actual amount of the material present in the test sample 414. The testing device 100 is capable of changing parameters for testing based on the test performed and the test cartridge assemblies 300 employed.

Since in the preferred embodiment, evaluation of the material within the test cartridge assembly 300 by the testing device 100 requires detecting the presence of light that may be emitted from the test sample 414 introduced by the test cartridge assembly 300, it is preferable to minimize or eliminate the amount of external or ambient light being introduced into the cartridge recess 152 of the testing device 100 during testing. To achieve this goal, the analysis portion 200 preferably prevents most or all environmental light emissions from reaching the sensor 206. The sensor 206 is arranged on a printed circuit board (“PCB”) 208, which is positioned under the analysis portion housing 204. Minimizing such environmental light emissions from reaching the sensor 206 prevents an erroneous output from the sensor 206.

The analysis portion frame 202 and the hinged lid 104 are preferably made of a generally rigid, opaque solid material such as aluminum in order to reflect or absorb all measureable light incident on the material, or some other such opaque solid material well known to those of ordinary skill in the art. The base 204B of the analysis portion housing 204 contains a rectangular cutout 214 on a lower surface. A viewing window 216 is mounted in the rectangular cutout 214. The viewing window 216 is preferably made of an optics grade transparent solid material, such as quartz glass or another transparent solid material, as is well known to those skilled in the art. The sensor 206 is positioned beneath the viewing window 216, allowing light to pass from the test cartridge assembly 300 through the viewing window 216 to the sensor 206 with a minimal amount of light absorption or reflection. Therefore, the sensor 206 receives the maximum signal possible through the viewing window 216.

In the preferred embodiment, the sensor 206 is a light sensor, and even more preferably the sensor 206 is a photomultiplier tube (PMT), as will be described further with reference to FIG. 12. The PCB 208 further includes an RFID communications circuit 210, a high voltage power supply 218 for use with the sensor 206, and other light sensing circuitry 1200, as will be described further below with reference to FIG. 12. Preferably, the RFID communications circuit 210 is positioned beneath an area of the cartridge recess 152 that aligns with an RFID tag 508 (FIG. 5B) within the test cartridge assembly 300 when the test cartridge assembly 300 is introduced into the cartridge recess 152.

A sensor shield 220 is positioned to substantially surround the sensor 206. The sensor shield 220 isolates the sensor 206 from electromagnetic and magnetic interference. The sensor shield 220 is preferably made from a generally rigid, solid conductive material with high magnetic permeability such as mu-metal or another such solid conductive material, as is well known to those skilled in the art. One of the walls of the analysis portion housing 204 contains a hollow protrusion 222 extending into the cartridge recess 152, which mates with a recess in the test cartridge assembly 300. The hollow protrusion 222 allows a piston 224 and piston rod 224A, which engages a fluid displacement mechanism 900 (FIG. 9) in the test cartridge assembly 300, to pass therethrough and contact with a plunger 424 (FIG. 4B) of the test cartridge assembly 300.

The piston 224 is preferably made of a generally rigid, polymeric material such as polystyrene or another similar polymeric material, as is well known to those skilled in the art. The piston 224 is actuated by a motor 226. In the preferred embodiment, the motor 226 is a linear stepper motor. However, other actuators, such as pneumatic pistons, servos, or the like may be used without departing from the scope of this invention. The piston 224 is engaged to the motor 226 via a threaded shaft 226A on the motor 226 coupled to an integral threaded hole (not shown) within the piston 224. In the currently preferred embodiment, the motor 226 is a HAYDON-KERK model 19542-05-905 stepper motor. In order to reduce the introduction of noise from the motor 226 into the analysis portion 200, the motor 226 is located outside of the analysis portion housing 204, not in close proximity to the sensor 206. This arrangement of the motor 226 relative to the sensor 206 decreases the possibility of the motor 226 electrically or electromagnetically interfering with the sensor 206.

A projection 228 protrudes from the piston 224, and aligns with a position detector 230, which is positioned outside of the analysis portion 200. At a certain stage of travel of the piston 224 (described below), the projection 228 triggers the position detector 230 to generate a position signal. In one embodiment, the position detector 230 trigger position corresponds with the second position of the plunger 424 shown in FIG. 10B. However, the trigger position may alternately correspond with the final position of the plunger 424, shown in FIG. 10C, or any other position in the path of the plunger 424. In a preferred embodiment, the position detector 230 is a photo-interrupter and the position detector 230 is triggered by the projection 228 blocking the path of light within the position detector 230, at which time, a signal is sent to the microprocessor 1102 to indicate the position of the piston 224. In this way, precision sensing of the position of the piston 224 can occur to ensure that there are no errors in the actuation of the test cartridge assembly 300. In the preferred embodiment, the position detector 230 is an OMRON model EE-SX4134 photo-interrupter. However, it will be appreciated by those skilled in the art that other types of devices may be utilized for the position detector 230 without departing from the scope of this invention.

The piston 224 includes a piston rod 224A extending therefrom which contains spaced pairs of radially outwardly extending annular flanges 232A-C in spaced locations along its length. Compressible sliding seals 234A and 234B are radially mounted between the annular flanges 232A and 232C, respectively. The sliding seals 234 are preferably made of an elastomeric material such as silicone, or some other such elastomeric material, as is well known to those skilled in the art. When the piston 224 is installed, the first sliding seal 234A, mounted between annular flanges 232A engages with the interior surface of the hollow protrusion 222 of the analysis portion housing 204 to create a fluid-tight seal that prevents liquids from entering into the lower analysis portion 200, from the cartridge recess 152, and reaching the electronic components on the PCB 208 beneath the analysis portion housing 204. The second sliding seal 234B, mounted between annular flanges 232C engages with the interior surface of a hollow channel through which the piston rod 224A passes into the analysis portion frame 202 to create a light-tight seal that prevents environmental (ambient) light emissions from entering the light sealed area of the analysis portion housing 204 along the path of the piston 224.

The piston rod 224A also contains a third pair of annular flanges 232B which engage a sliding shutter 236. The sliding shutter 236 is preferably constructed of a rigid, opaque, thin material, such as a formed stainless-steel sheet, for the purpose of keeping the analysis portion 200 low profile and sized to be portable. Alternately, the sliding shutter 236 may be constructed of a conductive material with high magnetic permeability, such as a mu metal in order to provide additional shielding to the sensor 206. When initially engaged by the piston rod 224A, the sliding shutter 236 passes between the sensor 206 and the viewing window 216. In this position, the sliding shutter 236 reflects or absorbs nearly all environmental light emissions that would otherwise reach the sensor 206 when the hinged lid 104 is open and the analysis portion 200 is exposed to ambient light. In the case that the sensor 206 is a PMT, the sliding shutter 236 protects the sensor 206, which is vulnerable to saturation and damage when fully exposed to ambient light levels. The sliding shutter 236 contains an aperture 238 that aligns with the sensor 206 at the start of a test. Preferably, prior to the beginning of a test, the sliding shutter 236 covers the sensor 206. It is desirable for the sliding shutter 236 to engage the piston rod 224A and make use of the motion of the motor 226 to slide into the position in which the aperture 238 is over the sensor 206 at the start of a test. This arrangement minimizes additional component costs, and further reduces the risk of electrical or electromagnetic interference.

Referring now to FIGS. 1 and 2, the analysis portion 200 is located within the housing 102 of the testing device 100. At least a portion of the analysis portion 200 is at least partially covered by the hinged lid 104 when the hinged lid 104 is in the closed position shown in FIG. 1A. The analysis portion 200 preferably includes the PCB 208 having the integral RFID communications circuit 210 that is configured to communicate via radio frequency with a unique Radio Frequency Identification (“RFID”) tag 508 of a test cartridge assembly 300 (FIG. 3). In the preferred embodiment, the RFID communications circuit 210 is a TEXAS INSTRUMENTS RFID communications IC model TRF7961. However, it will be apparent to those skilled in the art that other types of scanners or scanning devices, and other data transmission schemes, could alternatively be employed for providing information to the testing device 100 and/or writing information to the RFID tag 508 of the test cartridge assembly 300.

It should be appreciated by those of ordinary skill in the art that the precise structure of the analysis portion 200 and/or its components are merely that of a currently preferred embodiment and that variations may be made to the structure of the analysis portion 200 and/or its components without departing from the scope and spirit of the invention. Thus, the present invention is not limited to the precise structure of the analysis portion 200 described herein but is intended to encompass structural and/or operational variations, as well as other structures and arrangements which may perform the same, or substantially the same functions, as those of the current analysis portion 200.

The variations may include such structural changes as omitting an electromechanical motor, and instead relying on a user input force to actuate of the cartridge, actuating the test cartridge directly without the use of a piston, utilizing multiple motors for different actions, placing the motor within the light-sealed area of the analysis portion 200, or controlling the motor without precise position sensing. Further, the shape, arrangement and size of the test cartridge recess 152 in the analysis portion housing 204, the lid protrusions 104 a, and locking latches 104 b may vary from what is shown and described herein without departing from the scope of this invention. All that is necessary is that the cartridge recess 152 must compliment and conform to the size and shape of the test cartridge assembly 300 such that the cartridge recess 152 may accept an introduced test cartridge assembly 300.

Similarly, light sensing by the sensor 206 may be replaced by a different signal detection scheme, as is well known to those skilled in the art, without departing from the scope of this invention. For example, detection of electrical signals could be employed for evaluation of the test result. In this case, it may be preferable to minimize or eliminate extraneous sources of noise other than light. Structural changes to the analysis portion 200 that facilitate the minimizing or eliminating such extraneous sources of noise other than light are within the scope of this invention.

Referring now to FIGS. 3A and 3B, there is shown the test cartridge assembly 300 for use with the testing device 100 according to the preferred embodiment of the present invention. Preferably, the test cartridge assembly 300 is a single-use, disposable cartridge that is employed for receiving a small quantity of a sample 414 (FIG. 4B) gathered from foodstuffs or other sources for a test to be performed by the testing device 100. Therefore, the test cartridge assembly 300 is preferably configured to be fixedly insertable into the testing device 100 for the duration of a performance of a selected test. Even more preferably, each test cartridge assembly 300 contains all the necessary reagents 504, 506 (FIG. 5B) and the like for the performance of a single test, as will be described further herein.

As shown in FIG. 3A, the test cartridge assembly 300 preferably comprises two separate portions, a test cartridge base 400, described further with reference to FIG. 4, and a reservoir card 500, described further with reference to FIG. 5. The test cartridge base 400 and the reservoir card 500 are configured to interact with one another for the performance of a test by the testing device 100. The reservoir card 500 is designed as a separate part from the test cartridge base 400 in order to occupy a minimal volume, and to achieve a high packing density. Packing density is a critical consideration for the occasions when the necessary reagents 504, 506 require storage at low or below freezing temperatures. However, an integrated, single unit, test cartridge assembly 300 may similarly be produced, and is within the scope of this disclosure.

The test cartridge base 400 is configured to accept the separate reservoir card 500 in a slot 402 (FIG. 4A) at a first end 400 a of the test cartridge base 400. The reservoir card 500 is specifically designed to provide a convenient, small sized storage and delivery vehicle for one or more biosensors (reagents 504, 506). As shown in FIGS. 3A and 3B, a user assembles the reservoir card 500 into the test cartridge base 400 by sliding the reservoir card 500 into the slot 402. Once the reservoir card 500 is inserted into the test cartridge base 400, the reservoir card 500 is fixedly attached to the test cartridge base 400. The permanent attachment features 502 prevent misuse of the test cartridge base 400, such as reuse of the test cartridge base 400 with multiple reservoir cards 500. Contamination of the test cartridge base 400 and/or reservoir card 500 is thereby avoided. The reservoir card 500 may be attached to the test cartridge base 400 using any known suitable mechanical attachment device or member, such as the one-way attachment features 502 (FIG. 5B).

The test cartridge base 400 preferably does not contain any test-specialized components and may therefore be common to a plurality of test types. As such, the test cartridge base 400 should be compatible with multiple types of reservoir cards 500. As shown in FIGS. 4B and 9, the test cartridge base 400 contains a reaction chamber 404 and a fluid displacement mechanism 900, which together occupy a relatively large volume in comparison to the volume of the reservoir card 500. Referring to FIGS. 5A and 5B, the reservoir card 500 contains all of the necessary reagents 504, 506, and the like, for performing a single test by the testing device 100. Accordingly, a plurality of distinct types of reservoir cards 500, each having one or more distinct reagents 504, 506 for performing a particular test type, may be provided. Preferably, the reaction chamber 404 facilitates a proper mixture of the sample 414 and the reagents 504, 506, while minimizing damage to the living cells which comprise the reagents 504, 506. The reaction chamber 404 also maximizes gathering the light that the reagents 504, 506 emits to the sensor 206 in the presence of an offensive analyte or to confirm the proper functioning of the first phase of the test.

As best shown in FIG. 4B, the test cartridge base 400 is comprised of a generally rectangular housing 401 with an integral hinged lid 408. The rectangular housing 401 is preferably formed of a generally rigid, preferably polymeric material, such as polypropylene or another such polymeric material well-known to those skilled in the art. An adhesive-backed film 410 is used to enclose fluid channels 406 formed in the planar surface 400 b of the housing 401 for the sealed passage of reagents 504, 506 and/or air between the reservoir card 500 and the test cartridge base 400. The test cartridge base 400 housing 401 also includes an integral reaction chamber 404 for deposition of the sample 414, and eventual mixing of the sample 414 with the reagents 504, 506 for performing the desired test.

When the test cartridge assembly 300 is placed in the cartridge recess 152, the bottom surface 404 a of the reaction chamber 404 within the test cartridge base 400 housing 401 is aligned with the light sensor 206. Referring to FIG. 3C, the reaction chamber 404 is sealed on the bottom surface with a lens 412. The lens 412 is preferably formed of a rigid, preferably polymeric material such as polycarbonate or some other such polymeric material well-known to those skilled in the art. The lens 412 material is preferably an optics grade transparent material in order to prevent unwanted light absorption or reflection between the reagents 504, 506 and the light sensor 206. In the preferred embodiment, the lens 412 is thermally welded to the test cartridge base 400 housing 401 in order to provide a liquid-tight seal and minimize the introduction of contaminants into the reaction chamber 404. Referring to FIGS. 4A and 4B, the reaction chamber 404 is open to the top surface 400 b of the test cartridge base 400 housing 401 in order to allow a user to directly deposit the sample 414 (preferably in liquid form) into the reaction chamber 404.

The adhesive-backed film 410 is placed on the top surface 400 b of the test cartridge base 400 housing 401. The film 410 is preferably pre-scored or perforated 416 above the reaction chamber 404 in a way that allows the user to pierce through the film 410 using the tip of a deposition tool (not shown), such as a pipette for deposition of the sample 414 into the reaction chamber 404. The pre-scoring or perforation 416 of the film 410 is desirable in order to provide a visual cue to the user that they have completed the sample deposition step in the test process, or that the test cartridge assembly 300 was previously used and should be discarded. A compressible gasket 418 with adhesive backing 418 b is placed around the perimeter of the opening on the top surface 400 b to the reaction chamber 404 (surrounding the perforated or pre-scored area 416 of the adhesive backed film 410, see FIG. 4A). for the purpose of creating a fluid-tight seal when the integral test cartridge base 400 hinged lid 408 is closed. The integral test cartridge base 400 hinged lid 408 contains snap features 408 a, 408 b to retain the test cartridge base 400 hinged lid 408 in a closed position by interacting with catch slots 420 a, 420 b after the sample 414 has been deposited into the reaction chamber 404.

Still referring to FIGS. 4B and 3C, a central bore 422 is located within the test cartridge base 400 housing 401 that contains a plunger 424 as part of the test cartridge's fluid displacement mechanism 900, which will hereinafter be described in greater detail. The plunger 424 is preferably made of an elastomeric material, such as silicone rubber or some other such elastomeric material, as is well-known to those skilled in the art and is sized to sealingly engage the interior wall of the central bore 422. The top surface 400 b of the test cartridge base 400 housing 401 contains a relatively large vent overflow chamber 426 which communicates with the reaction chamber 404 by a vent channel 426A. The vent overflow chamber 426 is present to allow air to be displaced out of the reaction chamber 404 during the introduction of the reagents 504, 506, and contains features to contain any stray amount of liquid that may enter the vent channel 426A. Preferably, the vent overflow chamber 426 contains an absorbent material 428 utilizing an anti-microbial coating that the vented air must pass through as it exits the test cartridge base 400 housing 401. This ensures that any stray amount of liquid will be absorbed and contained within the vent overflow chamber 426, and any biological components will be destroyed.

As shown in FIG. 5B, the reservoir card 500 includes a plurality of fluid ports 516, which when the reservoir card 500 is inserted into the test cartridge base 400 housing 401 interface with a series of sealing features 702 (FIG. 7), thereby making connections with the reservoir card 500 when assembled. The sealing features 702 are recessed under a wall 401A (FIG. 7) in the test cartridge base 400 housing 401 for the purpose of preventing damage to the sealing features 702 and eliminating potential sites for easily contacted contaminants to be introduced to the reagents 504, 506.

It should be appreciated by those skilled in the art that the precise structure of the test cartridge base 400 and/or its components are merely that of a preferred embodiment, and that variations may be made to the structure of the test cartridge base 400 and/or its components without departing from the scope and spirit of the invention. Other structural and functional variations, such as, depositing the sample 414 in a location other than the reaction chamber 404 to be moved to the reaction chamber 404 at a later time, utilizing multiple parts to achieve the test cartridge base 400 housing 401, and reaction chamber 404 features, using a separate lid or closure scheme for the reaction chamber 404 after sample deposition, or alternatively locating the plunger 424 and/or other components of the fluid displacement mechanism 900 on the reservoir card 500 are all within the scope of this invention.

The reaction chamber 404 and fluid channels 406 that lead to the reaction chamber 404 within the test cartridge base 400 housing 401 are preferably designed to achieve several objectives. An inlet channel 802 (FIG. 8) for fluid entering the reaction chamber 404 is preferably tubular in shape with a diameter which is preferably small and tapers to become smaller at the inlet to the reaction chamber 404. This structure preferably increases the velocity of fluids entering the reaction chamber 404 to promote vigorous, and therefore homogenous, mixing due to the bulk motion of the of the reagents 504, 506 within the reaction chamber 404.

Referring to FIG. 8, a cross-sectional side elevational view of the test cartridge assembly 300 is shown. It is desirable to mix the reagents 504, 506 and sample 414 in a way to promote mixing beyond molecular diffusion, in order to minimize the duration of the test by ensuring that any infectious agent present in the sample 414 rapidly encounters the reagents 504 and 506. In the preferred embodiment, the minimum diameter of the inlet channel 802 is 0.75 mm. The inlet channel 802 is further preferably offset from the central axis of the reaction chamber 404 in order to promote a clockwise or counterclockwise rotational motion of the reagents 504 and 506 around the central axis of the reaction chamber 404 as the fluids are mixed in order to increase the homogeneity of the mixture.

In the currently preferred embodiment, the inlet channel 802 is approximately tangent to the interior surface of the reaction chamber 404. This is desirable in order to allow the incoming fluid to travel from the inlet channel 802 to the fluid level within the reaction chamber 404 while remaining in contact with the side surface of the reaction chamber 404, which allows for a minimally turbulent flow and minimal introduction of air bubbles into the mixed fluids. Bubbles are undesirable due to the unpredictable refraction of light they cause as light emitted by the reagents 504, 506 interacting with the sample 414 travels through bubbles within the mixed reagents 504, 506 or on the surface of the mixed reagents 504, 506.

In some embodiments of the invention, a stabilizer is included in the reaction chamber 404. The stabilizer may be, for example, Pluronic F68, which is used in cell cultures as a stabilizer of cell membranes by protecting from membrane shearing and additionally as an anti-foaming agent. Certain embodiments of this invention also include at least one additive, such as Pluronic F68, polyethylene glycol, methocel, or the like, located in the reaction chamber 404 for minimizing the formation of bubbles in the reaction chamber 404 during mixing of the sample 414 and the reagents 504, 506. This additive may further include a surfactant, such as Pluronic F68, Polyvinyl pyrolidone, Polyethylene glycol, Polyvinyl alcohol, Methocel (methyl cellulose), or the like. Some embodiments of the present invention also include a device for disrupting individual cells of the sample 414 and particularly the infectious agent within the sample 414 prior to mixing the sample 414 with the reagents 504, 506 for purposes of amplifying the light signal generated by the reagents 504, 506 reacting with an infectious agent within the sample. An example of such a device is a sonicator (not shown).

The axis of the inlet channel 802 is preferably angled above horizontal in order to provide a partially downward direction to the incoming fluid flow to ensure that the reagents 504, 506 are mixed with the fluid residing at the bottom of the reaction chamber 404. In the currently preferred embodiment, the inlet channel 802 is angled above horizontal at an angle of approximately thirty (30) degrees, and additionally the optimum functional range occurs between fifteen (15) degrees and sixty (60) degrees above horizontal. It will be appreciated by those skilled in the art that the arrangement, position and structure of the inlet channel 802 may be varied without departing from the scope of the present invention.

Alternatively, if desired, the reagents 504, 506 may be introduced to the reaction chamber 404 using alternative fluid delivery techniques, such as a vertical channel (not shown) that delivers the reagents 504, 506 to the reaction chamber 404, or delivering the fluid reagents 504, 506 directly on the central axis of the reaction chamber 404 in order to create a column of reagent flowing into the reaction chamber 404 promoting mixing through entrainment. Furthermore, a user may deliver the one or more reagents 504, 506 manually in the same way and, for example, at the same time as the sample 414 is deposited into the reaction chamber 404.

The reaction chamber 404 preferably has a shape that maximizes the amount of photons that are reflected toward the bottom of the reaction chamber 404 to allow the photons to be read by the sensor 206 positioned under the reaction chamber 404 in the analysis portion 200. In the preferred embodiment, the shape of the reaction chamber 404 is a revolved section to facilitate the clockwise or counterclockwise motion of the mixing fluids 414, 504, 506 around the central axis of the reaction chamber 404. Alternatively, if desired, a reaction chamber 404 shape other than a revolved section, such as a rectangular or irregular shape, could be used. In the preferred embodiment, the revolved section used to form the reaction chamber 404 is a portion of an ellipse. This elliptical shape is desirable in order to aid in collecting stray light emitted by the reagents 504, 506 reacting with the sample 414 and reflecting this light toward the surface of the light sensor 206. The reaction chamber 404 shape is preferably generally parabolic. The reaction chamber 404 may be a revolved half of an ellipse with an opening at the top of approximately 2.5 mm, and with the lower diameter located at the major or minor axis of the ellipse and equal to approximately 8 mm.

The surface of the reaction chamber 404 is preferably reflective, in order to further enhance the light collection properties of the elliptical shape. In the preferred embodiment, the maximum diameter of the sensing surface 206 a of the sensor 206 is limited in order to achieve the maximum signal to noise ratio of the output of the light sensing circuit 1200 (FIG. 12). The diameter of at least the bottom of the reaction chamber 404 is designed to approximately match the diameter of the sensor 206, which influences the elliptical shape that can be achieved in a reaction chamber 404 designed to hold a specific volume of fluids for a given test type. In the preferred embodiment, the preferable reaction chamber 404 surface color is a partially diffusing white, due to the additional light collection that occurs when light that would not otherwise be reflected directly to the sensor 206 surface 206 a is partially diffused by the white surface and a fraction of the light is directed toward the sensor 206 surface 206 a. Alternatively, other surface finishes, colors, and materials such as a near-mirror finish aluminum, or a transparent material could be used.

It is desirable for the reaction chamber 404 material to be minimally phosphorescent in order to prevent light emitted from the reaction chamber 404 itself from overwhelming any emitted light from the reagents 504, 506 reacting with the sample 414 and thereby preventing or otherwise affecting detection. Although white polymeric materials such as acrylonitrile butadiene styrene or other such polymeric materials have been found to exhibit a low level of phosphorescence, the additional light collection provided by the combination of light reflection and diffusion has been found to be a benefit to the signal to noise ratio of the output of the light sensing circuit 1200.

As shown in FIGS. 5A-5C, the reservoir card 500 is comprised of a generally rectangular housing 501. The reservoir card 500 housing 501 is preferably formed of a generally rigid, preferably polymeric material such as polypropylene or some other such polymeric material well-known to those skilled in the art. Referring to FIG. 5B, fluid storage channels 510, 512 are formed into the upper surface 501 a of the reservoir card 500 housing 501 in order to provide storage for all of the necessary reagents 504, 506 for performing a specific test type.

In the preferred embodiment, the first reagent 504 is a biosensor reagent capable of emitting light when a specific pathogen or set of pathogens is detected, and the second reagent 506 is a positive control sample, such as anti-Immunoglobulin M (anti-IgM) or digitonin. The second reagent 506 is utilized for the purpose of rapid activation of the first biosensor reagent 504 after the duration of the initial test as a verification of the viability of the biosensor reagent 504. The second reagent 506 functions as a negative result control test and is therefore optional. That is, the test may be performed without the presence and/or use of the second reagent 506, but in its absence, the accuracy of the test result may be difficult to verify.

The fluid storage channels 510, 512 for storing the reagents 504, 506 are formed to provide a small cross-sectional area, preferably of approximately 1 mm width and 1 mm height. The small cross-sectional area allows the stored reagents 504, 506 to be easily displaced out of the fluid storage channels 510, 512 using one or more additional fluids, such as air. A smaller cross-sectional area is also desirable due to the resulting decrease in thawing time in the occasions where the necessary reagents 504, 506 are required to be stored frozen and are thawed immediately before testing. A thin cover 514, preferably of a polymeric material or the like, is bonded to the reservoir card 500 housing 501 to enclose the fluid storage channels 510, 512 and provide a fluid-tight seal on the top surface 501 a of the reservoir card 500 housing 501.

Referring to FIG. 5B, the reservoir card 500 housing 501 also contains a recessed area (not shown) on the bottom surface 501 b to contain the RFID tag 508. The recessed area serves to prevent damage from accidental contact with sensitive components of the RFID tag 508. The RFID tag 508 is located within or is secured to the reservoir card 500 in order to minimize user error in associating test cartridge data 300 stored on the RFID tag 508 with the necessary reagents 504, 506 required for specific test types. Use of RFID technology is preferable in order to automate the data transfer between the test cartridge assembly 300 and the testing device 100, thereby minimizing sources of possible user error.

An end face 501 c of the reservoir card 500 housing 501 contains a plurality of fluid ports 516 a-516 d, which make fluid connections with the test cartridge base 400 housing 401, when assembled into the test cartridge assembly 300. Each of the fluid ports 516 are attached to a compressible gasket 518 with an adhesive backing or the like around the perimeter of each fluid port 516. The compressible gaskets 518 create a fluid-tight seal with the test cartridge base 400 housing 401 when the reservoir card 500 is properly installed in the test cartridge base 400 as shown.

In order to prevent contaminants from contacting the fluid ports 516, and to prevent damage to the compressible gaskets 518, the end face 501 c of the reservoir card 500 housing 501 is initially covered with a film 520 (see FIG. 5A). In the preferred embodiment, the film 520 is a Polyethylene terephthalate film, or some other flexible polymeric film capable of creating a liquid tight seal with the reservoir card 500 housing 501. The film 520 has selectively applied adhesive backing and is selectively bonded using the adhesive on a single side of the film 520 to the reservoir card 500 housing 501 in a way such that each fluid port 516 is individually sealed around its perimeter, and one end 520 a of the film 520 is permanently bonded to the top face 501 a of the reservoir card 500.

FIG. 6A is a magnified side elevational view of a portion of the reservoir card 500 in the initial arrangement of FIG. 5A with a folded-over film 520 covering the fluid ports 516. As shown in FIGS. 5B and 6A, the film 520 is laid back upon itself at point 520 b so that the remaining end of the film 520 is directed back to the top face 501 a of the reservoir card 500. The remaining end 520 c of the film 520 is permanently bonded utilizing the selectively applied adhesive to a carrier part 522. The carrier part 522 is preferably made of a generally rigid, polymeric material such as polypropylene, or another such polymeric material known to those skilled in the art.

FIG. 6B is a magnified side elevational view of the portion of the reservoir card 500 in the inserted arrangement of FIG. 5C with the folded-over film 520 retracted to reveal the fluid ports 516. As shown in FIG. 6B, any motion of the carrier part 522 away from the fluid ports 516 results in a peeling motion of the bonded film 520 from the fluid port end 501 c of the reservoir card 500 housing 501 which unseals and exposes the fluid ports 516 and their gaskets 518.

There are several actions that occur as the reservoir card 500 is assembled into the test cartridge base 400. As the reservoir card 500 is slid into the receiving slot 402 on the test cartridge base 400 housing 401, the carrier part 522 on the reservoir card 500 mechanically interferes with the top wall of the receiving slot 402 on the test cartridge base 400 housing 401. The reservoir card 500 is shaped so that it cannot be fully inserted into the receiving slot 402 of the test cartridge base 400 in a backwards or top-side-down orientation. When the reservoir card 500 is in the correct orientation, as the user continues to insert the reservoir card 500, the mechanical interference between the carrier part 522 and test cartridge base 400 housing 401 wall causes the carrier part 522 to move relative to the reservoir card 500 away from the fluid ports 516 (See FIG. 5C).

As described above, the motion of the carrier part 522 away from the fluid ports 516 of the reservoir card 500 causes a peeling motion of the film 520 in place over the fluid ports 516 of the reservoir card 500. The peeling of the film 520 exposes the fluid ports 516 and their gaskets 518 on the reservoir card 500 (See FIG. 5C). Preferably, the complete exposing of the fluid ports 516 occurs after the reservoir card 500 has been fully engaged with the receiving slot 402 on the test cartridge base 400 housing 401 so that the fluid ports 516 are protected by the top wall of the receiving slot and are never openly exposed to the external environment. This behavior is desirable to prevent contaminants from contacting the fluid ports 516 and becoming introduced to the reagents 504, 506.

As the reservoir card 500 moves fully into the receiving slot 402 on the test cartridge base 400 housing 401, referring to FIG. 7, sealing features 702 present on the test cartridge base 400 housing 401 come into contact with the gaskets 518 of the fluid ports 516 on the reservoir card 500, forming fluid-tight seals. In the presently preferred embodiment, the seal between the gaskets 518 and the sealing features 702 is a face seal. However, other types of seals or sealing features (such as luer seals) could alternatively be employed for providing a fluid-tight seal between the reservoir card 500 and test cartridge base 400 housing 401. Alternative sealing features could include a radially compressible gasket (not shown) forming an annular seal. When the reservoir card 500 has been fully inserted into the receiving slot 402 and the fluid-tight seals have been formed, one way attachment features 502 (FIG. 5B) on the reservoir card 500 housing 501 engage with complimentary retention features (not shown) on the test cartridge base 400 housing 401 in a manner well known in the art to permanently retain the reservoir card 500 in the assembled state with the test cartridge base 400, thereby creating the test cartridge assembly 300.

It will be appreciated by those skilled in the art that while a particular reservoir card 500 component arrangement has been described, the present invention is not limited to this particular arrangement. Possible alternative arrangements include use of only a single reagent, storage of reagents 504, 506 in a larger cylindrical volume, or alternative fluid port protective features, such as pierced films or foils and/or user removed coverings.

Referring to FIGS. 9, 10A, 10B and 10C, a fluid displacement mechanism 900 within the test cartridge base 400 is shown. FIG. 9 is a cross-sectional side elevational view of the test cartridge assembly of FIG. 3A introduced into the analysis portion 200. The plunger 424, which is located in the test cartridge base 400 housing 401, is preferably designed to move air that travels through the air channels 902A-902D in the test cartridge base 400 housing 401, through the sealing features 702 formed between the assembled reservoir card 500 and the test cartridge base 400 housing 401. When actuated by the piston rod 224A, the plunger 424 causes the reagents 504, 506 stored in the reservoir card 500 to be displaced into the test cartridge base 400. As described above, the plunger 424 is preferably actuated by the piston rod 224A in the analysis portion 200.

As they are displaced, the reagents 504, 506 are forced into the test cartridge base 400 housing 401, and eventually into the reaction chamber 404. The design utilizing air to displace the reagents 504, 506 from the reservoir card 500 enables the fluid displacement mechanism 900 components to be located in the test cartridge base 400 housing 401, which allows the reservoir card 500 to achieve a minimal volume to facilitate storage and transport of the reservoir card 500. In the preferred embodiment, the air channels 902A-D leading from the central bore 422 and plunger 424 are designed to produce a staged delivery of the reagents 504, 506 from the reservoir card 500 to the reaction chamber 404. Referring to FIGS. 10A-10C, the delivery of the reagents 504, 506 occurs as air is displaced from the central bore 422 through a series of air channel ports 902 that are alternately sealed, and then opened, as the plunger 424 moves along the central bore 422.

Referring to FIG. 10A, in the beginning or first stage, the plunger 424 is positioned at a beginning end 906A of the central bore 422. Flanges 908 of the plunger 424 initially seal off a first air channel port 902A, which is connected through a fluid port 516C to the storage area 512 for the second reagent 506 in the reservoir card 500 and isolate the first channel port 902A from the other channel ports 902B-D and the first reagent 504.

A second air channel port 902B is open and connected to a fourth air channel port 902D. A third air channel port 902C is open and connected to the first reagent 504 storage area 510. In the preferred embodiment, the first reagent 504 includes the biosensor used for performing the test on the sample 414. As the plunger 424 is actuated by the piston rod 224A, the plunger 424 travels further through the central bore 422, and displaced air from the central bore 422 travels through the third air channel port 902C, displacing the first reagent 504 from the reservoir card 500. The first reagent 504 flows into the test cartridge base 400 housing 401, and eventually into the reaction chamber 404 to mix with the sample 414 in the above-described manner.

As the plunger 424 moves through a second stage toward the second end 906B of the central bore 422, referring to FIG. 10B, the second air channel port 902B becomes sealed off by the flanges 908. However, the sealing of the second air channel port 902B has no effect due to the direct connection of the second air channel port 902B to the fourth air channel port 902D. When the plunger 424 reaches the second stage of FIG. 10B, the entire volume of the first reagent 504 will have been displaced from the reservoir card 500 to the test cartridge base 400 housing 401. At this time, the motion of the plunger 424 is paused with the second air channel port 902B sealed off for the duration necessary to complete the first phase of the test by the testing device 100. In one embodiment, the motion of the plunger 424 is paused for approximately sixty (60) to one hundred twenty (120) or more seconds. The amount of time the plunger 424 is paused preferably depends on the type of test being run by the testing device 100 and is determined based on information provided by a test cartridge 300 RFID tag 508 being read by the testing device 100 after insertion into the cartridge recess 152.

After the first phase of the test is completed, if the second test is to be performed, the plunger 424 is again moved by the piston rod 224A, causing the plunger 424 flanges 908 to seal off the third air channel port 902C and open the second air channel port 902B. As the plunger 424 continues to move through the central bore 422 toward the second end 906B, displaced air from the central bore 422 is forced to travel through the fourth air channel port 902D, to the second air channel port 902B, and through the central bore 422 in the clearance region between the plunger 424 and the central bore 422 surface to the first air channel port 902A. The displaced air that travels through the first air channel port 902A displaces the second reagent 506, which flows into the test cartridge base 400 housing 401, and eventually into the reaction chamber 404 in order to perform the second or negative result verification test phase.

The plunger 424 continues to move through the central bore 422, until contacting the second end 906B of the central bore 422, as shown in FIG. 10C. By this time the majority of the second reagent 506 will have been displaced and flowed into the reaction chamber 404. Upon completion of the plunger's 424 motion from the first end 906A to the second end 906B of the central bore 422, it is preferable that the plunger 424 may not be moved back toward the first end 906A. This one-way motion of the plunger 424 helps to prevent the test cartridge assembly 300 from being reused in a subsequent test.

The use of a single piston rod 224A and a single plunger 424 is desirable to limit the use of additional parts in the test cartridge assembly 300 and testing device 100 for cost reasons, manufacturing complexity reasons, and the reduction of sources of potential interference with the light sensor 206. However, it should be appreciated by those of ordinary skill in the art that the precise structure of the fluid displacement mechanism 900 described above is merely that of a currently preferred embodiment and that variations may be made to the structure of the fluid displacement mechanism 900 without departing from the scope and spirit of this invention. Possible alternative arrangements of the fluid displacement mechanism 900 include utilizing multiple motors to control one specific actuation or more per motor, utilizing multiple plungers to displace one or more reagents 504, 506 per plunger, using plungers to directly displace reagents 504, 506 instead of using air as an intermediary, or using an alternate means of displacing the reagents 504, 506, such as a compressible membrane or blister pack.

Referring to FIG. 11, a functional schematic hardware block diagram 1100 of the electrical/electronic and other related components of the preferred embodiment of the testing device 100 is shown. Operation of the testing device 100 is controlled by a microprocessor 1102. In the preferred embodiment, the microprocessor 1102 is an applications processor, such as the FREESCALE SEMICONDUCTOR model number MCIMX255AJM4A processor, which implements the ARM926EJ-S core with processor speeds up to 400 MHz. Even more preferably, the microprocessor 1102 includes an integrated 10/100 Ethernet controller and a Universal Serial Bus (USB) physical layer (PHY) 1108B. The microprocessor 1102 provides user defined, general purpose input/output (I/O) pins or ports for connection of additional peripheral devices (not shown), as hereinafter described. The microprocessor 1102 core operates between 1.34V-1.45V average power supply voltage from the power supply system 1126. It will be apparent to those skilled in the art that the microprocessor 1102 may be replaced by one or more microprocessors or other control devices such as FPGAs or ASICs, having different and/or additional features and functionalities without departing from the scope of this invention.

The built-in USB port 112 b and USB PHY 1108B integrated into the microprocessor 1102 are used to provide a USB communication port 112 b that allows the testing device 100 to communicate or receive communications from other USB devices (not shown). The testing device 100 uses a USB client protocol that allows the USB port 112 b to serve as a client to other USB devices (not shown). The external connection may be used for retrieval and installation of upgraded software, transmission of test records to remote devices (not shown), downloading test information and uploading test results to a host computer, or the like. Other driver circuitry could similarly be used if desired.

The testing device 100 further includes a flash read only memory (ROM) 1104, a dynamic random-access memory (RAM) 1106, and an Ethernet PHY interface 1108A, each of which access and are accessed by the microprocessor 1102 by way of individual parallel buses 1110 in a manner well known in the art. In the preferred embodiment, there are at least sixty-four megabytes (64 MB) of ROM 1104 and at least sixteen megabytes (16 MB) of SDRAM 1106. The RAM 1106 is a MICRON model MT48LC8M16A2P-7E:G integrated circuit organized by 2 Mb×16 I/Os×4 banks. The RAM 1106 supports software executing within the microprocessor 1102. The ROM 1104 is preferably a SAMSUNG model K9F1208U0C-PII300 NAND flash memory integrated circuit. The ROM 1104 is a persistent memory that is responsible for retaining all system software and all test records performed by the testing device 100. Accordingly, the ROM 1104 maintains data stored therein even when power to the testing device 100 is removed. ROM 1104 may be rewritten by a procedure well known to those skilled in the art, thereby facilitating the upgrading of system software of the testing device 100 executed by the microprocessor 1102, without having to add or replace any of the memory components 1104, 1106 of the testing device 100. Different models from the same or different manufacturers may alternatively be used for the ROM 1104 and/or the RAM 1106 if desired.

The microprocessor 1102 additionally has an integrated interface for a memory card Secure Digital expansion port and card reader 1112. The SD card expansion port 1112 is located within the testing device 100 to facilitate additional functionality in future iterations of the testing device 100 by introducing an SD memory card (not shown) having additional functionality stored thereon.

The Ethernet PHY interface 1108A is a model DP83640TVV integrated circuit from NATIONAL SEMICONDUCTOR and provides for a 100 MB per second connection to a local area network (LAN), computer (not shown), or other external device (not shown). The Ethernet PHY interface 1108A negotiates between a connected external device (not shown) and the microprocessor 1102 via its individual parallel bus 1110C.

The testing device 100 requires several regulated voltages to be supplied in order to function properly. The various voltages are provided by a multi-channel power management integrated circuit (PMIC) 1116. The PMIC 1116 addresses power management needs of up to eight (8) independent output voltages with a single input power supply. In the present embodiment, the PMIC 1116 is a FREESCALE MC34704 IC, but other power management circuits may alternatively be used. The PMIC 1116 provides standby outputs that are always actively supplying power to the real-time clock in the microprocessor 1102 and the battery monitor circuit (not shown).

The microprocessor 1102 controls its power supply system 1126 and enters into a sleep mode whenever the testing device 100 is inactive for a predetermined period of time (e.g., 10 minutes). At that time, most internal functions of the microprocessor 1102 are halted, thereby preserving the batteries 116. However, a real time clock (not shown) is kept running to maintain the correct date and time of day for the testing device 100. In addition, one or more sensors, such as the touch screen portion of the LCD 110, are preferably maintained in an active state so that the sleep mode may be exited by, for example, sensing the user depressing any portion of the touch screen, or opening the hinged lid 104 by depressing the actuator 106.

In the event that all electric power to the power supply system 1126 of the testing device 100 is removed, such as when the batteries 116 are replaced, a battery recovery backup (not shown) attached to the microprocessor 1102 maintains the minimal power necessary to power the real time clock so that the testing device 100 can maintain the correct date and time. The ability of the microprocessor 1102 to write to flash ROM 1104 is inhibited whenever power is being removed or restored to the testing device 100 until after the power supply system 1126 and microprocessor 1102 stabilize in order to prevent the accidental altering of the contents of the flash ROM 1102 while power is being cycled.

A first port of the microprocessor 1102 is used for connecting the microprocessor 1102 to the RFID communication circuit 210 via the sensor/RFID board interface 1118 and to the light sensing circuit 1200 (FIG. 12) for receiving data therefrom. A second port of the microprocessor 1102 is used for connecting the microprocessor 1102 to peripherals (not shown) via the Experiment Support Peripheral Interface 1120. The light sensing circuit 1200 will hereinafter be described in greater detail with reference to FIG. 12.

The light sensing circuit 1200 is capable of detecting multiple ranges and types of readings that are necessary for conducting the various types of tests performed by the testing device 100. The light sensing circuit 1200 includes a secondary microprocessor 1202, a fast pulse counter 1204, one or more analog amplifiers and filters 1206, a PMT 206, and a PMT high voltage power supply 218. The PMT 206 detects light signals from the test cartridge assembly 300 on an active surface, and outputs current pulses to the light sensing circuit 1200. In the preferred embodiment, once the reagent 504 has mixed with the sample 414, the PMT 206 begins to analyze the light signature for photons that are not associated with normal radiation, photon emission from the test cartridge base 400 housing 401, and other mechanical noise from the testing device 100. The output current pulses are converted by the light sensing circuit 1200 and relayed by the secondary microprocessor 1202 in a digital format that is sent to the main microprocessor 1102 for analysis.

The spectral response range of the PMT 206 varies from the ultraviolet range to the visible light range (230 nm-700 nm) with a peak response at 350 nm and a photosensitivity response time of 0.57 ns. In the present embodiment, the PMT 206 a model R9880U-110 and high voltage power supply 218 is a model C10940-53, both manufactured by HAMAMATSU PHOTONICS. The secondary microprocessor 1202 is preferably a TEXAS INSTRUMENTS model MSP430F2013IPW processor.

The secondary microprocessor 1202 provides a consistent interface for transmitting data to the main microprocessor 1102. Accordingly, while it is desirable to include the secondary microprocessor 1202 in the testing device 100 within the light sensing circuit 1200 in order to provide future flexibility and ease in implementing additional or alternative sensors 206, or scaling up the light sensing circuit 1200 to include multiple detectors, the secondary microprocessor 1202 is optional. That is, the functionality of the secondary microprocessor 1202 may alternatively be performed by the microprocessor 1102. In this case, the sensor 206 could be connected directly to a serial port on the microprocessor 1102.

PMTs 206 are sensitive to sources of interference, such as temperature changes, electrical fields, magnetic fields, and electromagnetic fields. Thus, the area of the sensing surface of the PMT 206 is susceptible to the output of unwanted signals, or background noise, due to these and other sources of interference. In the preferred embodiment, the diameter of the sensing surface of the PMT 206 is limited to 8 mm in order to limit the generation of background noise signals and increase the signal to noise ratio (SNR) of the output of the light sensing circuit 1200. It will be apparent to those skilled in the art that other PMTs 206 and high voltage power supplies 218 may alternatively be utilized.

Returning to FIG. 11, the LCD 110 is driven by a LCD controller integrated in the microprocessor 1102, which generates the required signaling format to the LCD 110. Accordingly, the LCD 110 is connected to general purpose input/output ports of the microprocessor 1102 via the display/touch panel interface 1122. The LCD 110 preferably includes an on-board drive circuit (not shown) that interfaces to the input/output ports of the microprocessor 1102 via standard data and control signals. The touch screen of the LCD 110 utilizes a four-wire connection for communication with the microprocessor 1102. A speaker 1124 may be connected to the microprocessor 1102 to audibly output sounds, such as warning and error messages, and the like to the user.

It should be appreciated by those skilled in the art that the various electrical/electronic components shown in FIGS. 11 and 12 are merely one illustration of the electrical/electronic components of the preferred embodiment of the present invention. Other components may be substituted for or added to any of the components shown without departing from the scope of this invention. In other words, the present invention is not limited to the precise structure and operation of the electrical/electronic and related components shown in FIGS. 11 and 12.

Referring to FIG. 16, a flowchart of steps in which the test cartridge assembly 300 is utilized in conjunction with the testing device 100 for performing a test according to the preferred embodiment of this invention is shown. Before a test begins, a reservoir card 500 is manufactured, preferably outside of the test setting. Engineered B cells are grown at step 1610. The grown cells are charged with coelenterazine at step 1612, and excess coelenterazine is removed at step 1614. A cell stabilizer, such as pluronic F68 is added at step 1616, and a cryopreservative, such as dimethyl sulfoxide (DMSO), is added at step 1618 to complete creation of the biosensor (i.e., reagent 504). The cells are loaded into the reservoir cards 500 at step 1620. At step 1622, the positive control sample (i.e., reagent 506), such as anti-IgM or digitonin, is loaded into the reservoir cards 500. The reservoir cards 500 are then frozen, stored and/or distributed to testing sites at step 1624. Preferably, the cards are frozen and stored at temperature below approximately negative forty degrees Celsius (−40° C.).

Once the cards have been distributed, before the test begins, at step 1626, the user may be required to prepare a reservoir card 500 of a selected test type by thawing the reservoir card 500 and the reagents 504, 506 contained inside using a specified thawing procedure. Preferably, a thawing procedure is specified when required for a specific reservoir card 500 test type. At step 1628, a user selects the (prepared) reservoir card 500 of the desired test type and assembles the reservoir card 500 into the test cartridge base 400 until the permanent attachment features 502 on the reservoir card 500 housing 501 engage with the retention features in the test cartridge base 400 housing 401. In the currently preferred embodiment, audible (i.e., a click) and/or tactile feedback is evident to the user due to the permanent attachment features 502 on the reservoir card 500 engaging the retention features on the test cartridge base 400 housing 401.

At step 1630, the user optionally prepares a sample 414 by, for example, fragmenting any infectious agent present in the sample 414 using sonication, pressure gradient, and/or enzyme treatment, or the like. Several techniques may be used, including: (i) an enzyme such as lipase to release O-antigens from the cell surface (part of LPS); (ii) sonication to fragment the cells; (iii) a French Press or equivalent to fragment the cells; or (iv) a chemical treatment to release LPS from the cells. At step 1632, the user employs a sample deposition tool to pierce the perforated film 410 on the test cartridge base 400 above the reaction chamber 404 and deposit a very small quantity (e.g., thirty micro Liters) of a sample 414 of a suspected infectious agent directly into the reaction chamber 404 within the test cartridge base 400. The user then removes the sample deposition tool and closes the test cartridge base 400 integral hinged lid 408, ensuring that the retention features 408 a and 408 b engage with the slots 420 a and 420 b on the test cartridge base 400 housing 401. The test cartridge base 400 hinged lid 408 is retained in the closed position, and the compressible gasket 418 on the top surface of the test cartridge base 400 is engaged by the lid 408 to form a fluid-tight seal. At this time, the reagents 504, 506 stored inside the reservoir card 500 must be fully thawed in order to proceed with the rest of the test. Alternatively, the user could assemble the reservoir card 500 into the test cartridge base 400 after depositing the sample 414 in the reaction chamber 404 or before the reagents 504, 506 are thawed. Further, the sample 414 may be deposited into the reaction chamber 404 after the test cartridge assembly 300 has been inserted into the testing device 100.

Referring to FIGS. 1C and 3C, the bottom of the test cartridge assembly 300 is designed to be placed into the cartridge recess 152 in order for the lens 412 of the reaction chamber 404 to align with the sensor 206. The test cartridge assembly 300 and cartridge recess 152 are preferably shaped in a way that the test cartridge assembly 300 cannot be fully inserted in an improper orientation and/or the testing device 100 hinged lid 104 will not be able to close if the test cartridge assembly 300 is introduced into the analysis portion 200 in an improper orientation.

When the user inserts the test cartridge assembly 300 into the cartridge recess 152 in the proper manner, a physical process begins a chain reaction of physical and electronic processes within the testing device 100 to perform the desired test on the sample 414 at step 1634 and, if necessary, a positive control test at step 1636. The user closes the hinged lid 104 of the testing device 100, which mechanically latches in the closed position. The testing device 100 is capable of detecting when the hinged lid 104 is closed, and sends a signal to the microprocessor 1102, which activates the RFID communication circuit 210 for data transmission to and/from the RFID tag 508 via the RFID communications circuit 210.

At this time, the RFID tag 508 located within the test reservoir card 500 is placed in the path of the RFID communications circuit 210 within the analysis portion 200. In the present embodiment, the RFID tag 508 is a RI-116-114A-S1 from Texas Instruments, which operates at 13.56 MHz and contains 256 bits of user memory for read/write functionality. The testing device 100 reads detailed information for the test to be performed from the test cartridge assembly 300 RFID tag 508 via RFID. Information which may be communicated to and from the RFID tags 508 includes test lot or sample origin, the specific test to be performed, information concerning the identity of a particular test cartridge, as well as other information. The testing device 100 also writes a value to the test cartridge RFID tag 508, which signifies that the test cartridge assembly 300 has been used to perform a test. The writing of the RFID tag 508 prevents the test cartridge assembly 300 from being reused in the same or any other compatible testing device 100 in the future. Referring to FIGS. 13A and 13B, the testing device 100 prompts the user to confirm the test type and to start the test via a user interface 1400 (FIG. 14) displayed on the LCD 110, which will hereinafter be described in greater detail.

Referring to FIGS. 2 and 9, when the user chooses to start the test, the microprocessor 1102 sends a signal to actuate the motor 226, which drives the piston 224 and piston rod 224A forward to engage the fluid displacement mechanism 900, and to complete the introduction of the first reagent 504 to the reaction chamber 404 in the manner described above. The piston rod 224A also preferably functions as a hinged lid 104 interlock. Thus, once the piston 224 begins to move under the force of the motor 226 at the start of the test, the piston rod 224A moves beneath the actuator 106. When the piston rod 224A is beneath the actuator 106, mechanical interference between the two prevents the user from pushing down the actuator 106 and opening the lid 104 as a precaution against user error while a test is in process. The piston rod 224A remains beneath the actuator until the test is complete and the piston 224 is fully retracted. Simultaneously to completing the first stage of the fluid displacement mechanism 900, the piston rod 224A moves the sliding shutter 236 to its second position which exposes the surface of the sensor 206 to light emitted from the reaction chamber 404 of the test cartridge assembly 300 via the sliding shutter aperture 238.

Since the reaction process preferably begins as soon as the fluid displacement mechanism 900 within the test cartridge assembly 300 completes the first reagent 504 introduction to the reaction chamber 404, the light sensing circuit 1200 is also activated at this time to detect any light emissions that may occur even before the user makes the appropriate data entry, as will hereinafter be described in greater detail. If the light sensing circuit 1200 detects an appropriate light signal, the microprocessor 1102 stores and reports a positive result, the light sensing circuit 1200 is turned off and the motor 226 moves to retract the piston 224 to its initial position.

The plunger 424 of the tested test cartridge assembly 300 remains at its final position even after the piston 224 has been retracted. The user may then open the hinged lid 104 by pressing the actuator 106 and remove the used test cartridge assembly 300 for proper disposal. The test sample 414 and the reagents 504, 506 are all sealingly contained within the test cartridge assembly 300. The user may also confirm a result of the test within the user interface (FIG. 15) displayed on the testing device 100 LCD. Alternatively, if a predetermined length of time (e.g., 60-120 seconds) elapses during the initial test and the light sensing circuit 1200 has not detected an appropriate light signal, the motor 226 preferably moves to drive the piston 224 further into the fluid displacement mechanism 900 until completion of the introduction second reagent 506 into the reaction chamber 404 for the performance of the second test, as described above.

If the light sensing circuit 1200 does not detect an appropriate light signal as a result of the second test, the microprocessor 1102 stores and reports an error message. However, if as a result of the second test the appropriate light signal is detected by the light sensing circuit 1200, the microprocessor 1102 stores and reports a negative result. At this time, the light sensing circuit 1200 is turned off and the motor 226 moves to retract the piston 224 to its initial position. The user may then remove the used test cartridge assembly 300 for proper disposal. At this time, the testing device 100 is reset and is ready for receiving another test cartridge assembly 300. Subsequent testing may be conducted in the same manner (using a new test cartridge assembly 300) as described above.

As previously discussed, the testing device 100 has the capability of performing a variety of different real-time (or near real-time) tests using a single disposable test cartridge assembly 300 containing a reservoir card 500 which has been specifically designated to perform a particular test. Each reservoir card 500 contains a predetermined reagent mixture 504, 506 for performing a particular test. The RFID tag 508 within the reservoir card 500, as well as the reservoir card labeling (not shown) identifies the particular test that reservoir card 500 is to perform, as well as the relevant control parameters for the particular test. In this manner, the testing device 100 is adapted for automatic customization, through software, for the performance of various tests.

An exemplary first reagent 504 is a biosensor reagent which includes a human B lymphocyte engineered to express a bioluminescent protein and at least one membrane-bound antibody specific for a predetermined infectious agent. With regard to biosensors, cell-based biosensor (CBB) systems that incorporate whole cells or cellular components respond in a manner that can offer insight into the physiological effect of an analyte. As will be appreciated by those skilled in the art, cell-based assays (CBA) are emerging as dependable and promising approaches for detecting the presence of pathogens in clinical, environmental, or food samples because living cells are known to be extremely sensitive to modulations or disturbances in “normal” physiological microenvironments. Therefore, CBB systems have been employed to screen and monitor “external” or environmental agents capable of causing perturbations of living cells (see, for example, Banerjee et al., Mammalian cell-based sensor system, Adv. Biochem. Eng. Biotechnology, 117:21-55 (2010), which is incorporated by reference herein.)

Compared with traditional detection methods (e.g., immunoassays and molecular assays such as PCR), a biosensor provides several advantages including, (i) speed, i.e. detection and analysis occurs in several seconds to less than 10 minutes; (ii) increased functionality, which is extremely important for reporting active components such as live pathogens or active toxins, and (iii) ease of scale-up for performing high-throughput screening.

An aequorin-based biosensor system is utilized with certain embodiments of the present invention. Aequorin is a 21-kDa calcium-binding photoprotein isolated from the luminous jellyfish Aequorea victoria. Aequorin is linked covalently to a hydrophobic prosthetic group (coelenterazine). Upon binding of calcium (Ca2+) and coelenterazine, aequorin undergoes an irreversible reaction, and emits blue light (preferably 469 nm). The fractional rate of aequorin consumption is proportional, in the physiological pCa range, to [Ca2+]. Application of the aequorin-Ca2+ indicator to detect E. coli contamination in food products was reported in 2003 (see, Rider et al. A B cell-based sensor for rapid identification of pathogens, Science, 301(5630):213-5 (2003), which is incorporated by reference herein). In Rider, engineered B lymphocytes were used to express antibodies that recognize specific bacteria and viruses. The B lymphocytes were also used to express aequorin, which emits light in response to the calcium flux triggered by the binding of a cognate target to the surface-antibody receptor. The resulting biosensor cell emitted light within minutes in the presence of the targeted microbes. To create such biosensor cells, antibody heavy and light chains with variable regions were cloned and expressed in a B-lymphocyte cell line. The resulting immunoglobulins become part of a surface B-cell-receptor complex, which includes the accessory molecules immunoglobulin Alpha (Igα or CD79a) and immunoglobulin Beta. (Igβ or CD79b). When the complex is cross-linked and clustered by polyvalent antigens, such as microbes, a set of signaling events quickly leads to changes in the intracellular calcium-ion concentration, which then causes aequorin to emit light. This mechanism essentially hijacks the B-cell's intrinsic capacity to specifically recognize the antigen presented in the E. coli by the B-cell membrane IgG antibody, and this binding triggers a transient Ca2+ influx to cytosol, which binds the aequorin proteins engineered in this B-cell, and subsequently emit blue light. See, Reiman, Shedding light on microbial detection, N England J Med, 349(22):2162-3 (2003), which is incorporated by reference herein, in its entirety.

Selection of an appropriate B cell is important to the described testing. Therefore, any proposed cell line should be tested to confirm that the B cell receptor signaling pathway is fully functional. Individual B cell clones having the aequorin gene should be tested to identify a particular clone with high aequorin activity, as significant variation from one clone to the next is possible (see, generally, Calpe et al., ZAP-70 enhances migration of malignant B lymphocytes toward CCL21 by inducing CCR7 expression via IgM-ERK1/2 activation, Blood, 118(16):4401-10 (2011) and Cragg et al., Analysis of the interaction of monoclonal antibodies with surface IgM on neoplastic B-cells, Br J Cancer, 79(5/6): 850-857 (1999), both of which are incorporated by reference herein in their entirety).

A high-aequorin expressing B cell is important for achieving high levels of sensitivity when using this detection system. In an exemplary embodiment, the receptor response for the biosensor was verified by using the Ramos human B cell line. Ramos cells are first transfected with the aequorin gene and the transfected cells were then selected for the aequorin expression for two weeks. Thereafter, mixed Ramos cells are charged with coelenterazine (CTZ), and stimulated with anti-IgM Ab. The elicited flash signal is captured by a luminometer.

As shown in FIG. 17, anti-IgM stimulation causes an expected sizeable and prolonged flash (from 45 to 65 seconds). In FIG. 17, the Y-axis represents the amount of light flashing, and the X-axis represents the reaction time in seconds. At thirty (30) seconds, the anti-IgM solution is injected into the Ramos-aequorin cell solution. The first spike (from 30-37 seconds) is a noise signal, and the second larger and longer peak is the biological response to anti-IgM stimulation. To improve the overall signal/noise ratio, the CTZ is removed from the CTZ-charged Ramos-aequorin cells solution. Removal of CTZ from the cell solution decreases the noise signal from around one hundred fifty (150) to about fifty (50), without significant compromise of the amount of the true peak signal.

In accordance with the present invention, an exemplary protocol for cell handling and flash-testing includes: (i) culturing Ramos-aequorin cells with a regular culture medium and keeping these cells healthy (i.e., viability >98%); (ii) charging the Ramos-aequorin cells with CTZ at a final concentration of 2 μM, the cell density being 1-2 million per milliliter; (iii) charging the cells at 370° C. with 5% CO₂ in an incubator for at least 3 hours; (iv) removing the charging medium containing CTZ; (v) flash testing by taking 200 μL cell solution plus 30 μL stimulants (anti-IgM) and reading with a luminometer; and (vi) confirming the CTZ and aequorin functionality by adding 30-40 μL digitonin (770 μM).

The testing device 100 is preferably controlled by an operating system executed by the microprocessor 1102. In the present embodiment, the operating system is preferably a custom designed and programmed application running in the Linux environment. The operating system provides input/output functionality, and power management functions, as described. The custom application includes a simple, menu-based user interface, as shown in FIGS. 14 and 15; parameter-driven functions to control and analyze the tests performed by the testing device 100; and a file system to store test protocols and results. Stored test results can be recalled, displayed or printed out. The software allows for the addition of protocols for new tests through file downloading, or the like.

The user interface 1400 of FIG. 14 is preferably menu driven, with a series of items selectable by a user using menus provided on the touch screen LCD 110. Preferably, the user interface 1400 presents a series of choices that allows navigation to and through each specific test until completion thereof. In the present embodiment, the user interface 1400 allows the user to return to the previous screen by using a back key provided on the LCD and touch screen. However, use of the back key while testing is not allowed unless the test is cancelled or aborted. A selected action may proceed through a series of steps with each step being indicated by a new prompt to the user.

FIGS. 13A and 13B are a flowchart showing the basic flow of a preferred embodiment of the computer software employed by the testing device 100. It will be appreciated by those skilled in the art that the software may function in a slightly or completely different manner than the manner shown in FIGS. 13A and 13B, which is included merely to illustrate a currently preferred way for the software to function.

The process begins at step 1300, where a splash screen is presented to the user on the display 110 while the application completes loading on the testing device 100. At step 1302 and 1304, a user is prompted with a user name and password entry process. The testing device 100 verifies that the entered user name and password are valid, and proceeds to a home screen 1400 (FIG. 14) at step 1306. A user identifier (e.g., a five-digit code) uniquely identifying the user performing the test is preferably stored by the testing device 100 as part of a test record.

The user selects one or more actions and/or functions of the testing device 100 to be performed from the home screen 1400, including running a test (step 1308) by inserting a test cartridge assembly 300, reviewing logged results (step 1310) by pressing Test Log button 1402 or configuring settings (step 1312) such as Time Zone (Step 1330) or Language (Step 1332) by pressing button 1404. Preferably, the user selects the desired action using the touch screen LCD 110 of the testing device 100.

If the user inserts a test cartridge assembly 300 into the testing device 100 and closes the hinged lid 104, the RFID communications circuit 210 is activated after the hinged lid 104 is closed, and the RFID tag 508 or other identification on the installed test cartridge assembly 300 identifies the type of test that the testing device 100 is to perform.

Preferably, each RFID tag 508 stores a character string, which encodes the particular type of test for the test cartridge assembly 300, an expiration date for each test cartridge assembly 300, a test cartridge assembly 300 serial number, which may include a testing solution lot number, whether the test cartridge assembly 300 has previously been tested within a testing device 100, as well as other information pertaining to a particular test cartridge assembly 300. Taken together, the information presented in the RFID character string uniquely identifies each test cartridge assembly 300. The test cartridge assembly 300 information is entered into the testing device 100 when the test cartridge assembly 300 is inserted into the cartridge recess 152 in the analysis portion 200 and the hinged lid 104 is closed. The process checks the scanned test cartridge RFID tag 508 data to confirm that the test cartridge has not been used before. RFID tag 508 data scanned from the test cartridge are accepted as valid if the RFID communications circuit 210 detects no RFID transmission error during the scanning process and the data format of the RFID tag 508 is valid. Upon determining that the hinged door 104 is closed and that the data read from RFID tag 508 is valid, the Run test option of step 1308 is automatically selected, and the user is prompted to confirm that the testing device 100 is to run the test.

While the test begins, the user begins the required data entry. The user is prompted to enter the specific numeric code of the sample 414 into the touch screen LCD 110 at step 1314, where the user is prompted to enter a “Sample/Location” type. In the preferred embodiment, the numeric code of the sample 414 comprises a five-digit number that relates to a lot or environment of the sample 414. If the user selects “Sample,” at step 1316, the user is prompted to enter a lot number using the touch screen LCD 110. If the user selects “Location,” at step 1318, the user is prompted to enter a location using the touch screen LCD 110.

Upon receiving the sample specific code, the information received from the RFID tag 508 of the test cartridge assembly 300 and the received user data entry are compared to all stored test records, as well as the data received from the RFID tag 508 signifying whether the test cartridge assembly 300 has previously been tested, and rejects the test cartridge assembly 300 if that test cartridge assembly 300 has been tested before.

The information read from the RFID tag 508 is also used to identify the particular test to be performed by the testing device 100, and to select the appropriate test protocols. Protocols to be selected include test timing, light reading requirements from the light sensing circuit 1200, and the like for the particular test to be performed. The parameters from a test control table stored in the ROM 1104 specify how each step of the test data acquisition and analysis is to be performed, including alternate software routines where necessary. In this manner, new or modified test parameters can be installed by downloading new test control tables and, if necessary, supporting software modules, without modification of the basic operating or application software. Information from test control tables is stored in the ROM 1104 for each diagnostic test which could potentially be performed utilizing the testing device 100. In alternate embodiments, additional information relating to the test samples 414 may also be included in the test initiation process of the testing device 100. Such additional information may include handling requirements, quarantine requirements and other anomalous characteristics of test samples 414.

The testing device 100 performs the test on the sample 414 while the user enters the sample 414 specific numeric code and continues to perform the test after the user has completed the required data entry. The test is preferably only completed after the user completes the required data entry. Applying force to open the hinged lid 104, or failing to complete data entry results in a failed or aborted test. Preferably, the users of the testing device 100 understand that the testing device 100 requires that all data entry be fulfilled and that the hinged lid 104 must remain closed to minimize failed or aborted tests.

At step 1320, a status of the test is shown to the user. The testing device 100 displays the status information to the user to confirm that the test is in process until the test is complete. Test information, whether prospective, in process or completed, is displayed on the LCD screen 110 in a fixed, text format that includes the test cartridge assembly 300 identifying information described above. Elements of the test record which are not yet completed are either left blank or displayed as “in progress” until the test is completed. Preferably, the user cannot perform other functions on the testing device 100 while a test is running. However, in other embodiments, the software may be altered to allow the user to perform other tasks on the testing device 100, such as reviewing a test log, while a test is being performed.

If during the test, it is determined that an appropriate light signal is detected by the sensor 206, the process proceeds to step 1322, where a positive result is reported, and the user is prompted to confirm. Once the user confirms, the user is prompted to re-enter the Lot/Location number at step 1324. If the Lot/Location number matches, the test data is logged and the process returns to the home screen of step 1306. If at step 1320, an appropriate light signal is not detected by the sensor 206, the process checks whether an appropriate light signal is detected for the negative control test. If so, the negative result is reported, as shown in the Negative Result screen 1500 of FIG. 15 and the user is prompted to remove the cartridge at step 1326. At this point, no RFID signal is detected, and the test data is logged, with the process returning to the home screen of step 1306.

In addition, a test can be aborted by the software at any stage if, for example, the sensor 206, the motor 226, or any other hardware failure is detected or if the hinged lid 104 is opened. If at step 1320, such an issue is detected, a test error is reported at step 1328, and the user is prompted to remove the used test cartridge assembly 300. Once the test cartridge assembly 300 is removed, no RFID signal is detected by the RFID communications circuit 210, the error data is logged in ROM 1104, and the process returns to the home screen 1400 of step 1306. Similarly, the test can also be cancelled by the user at any stage until the test results are reported and stored. Aborted and cancelled tests are recorded in the test result file and stored in the flash ROM 1104 to prevent reuse of a previously used test cartridge assembly 300.

Test results are stored in the flash ROM 1104 in text form, preferably, as displayed on the touch screen LCD 110. Each test record preferably includes all of the above identified test information, including the identification of the test sample 414, the particular test performed, the date and time of the test, user ID and either a standard result or an identification that the test failed due to an error or was aborted.

All test results from either successfully completed or failed tests are stored in the flash ROM 1104. The user can recall the test results from the flash ROM 1104 to display on the touch screen LCD 110. Preferably, the flash ROM 1104 is large enough to store a substantial number of test records (e.g., five thousand records), preferably corresponding to the number of tests which could be expected to be performed in at least a week of testing by the testing device 100. It is contemplated that the user cannot delete records stored in the flash ROM 1104 in order to prevent unauthorized tampering with the test results. However, if the flash ROM 1104 is completely filled, the testing device 100 may automatically transition out of test mode and prompt the user to begin uploading data to a remotely located computer (not shown) via the interface ports 112. Once the upload is complete and the test records are deleted from the flash ROM 1104, the user may again perform tests using the testing device 100.

Conservation of battery power is an important concern which is addressed by the operating software at two levels. First, the current battery charge level is provided to the user on a periodic or continuous basis. The software also provides specific prompts to the user to initiate a recharging of the batteries 116 when the battery monitor circuit indicates that the batteries 116 charge level has fallen below a predetermined safe limit. Further, the software precludes the initiation of a new test when the battery charge level in the batteries 116 is too low for the safe completion of a test without risking a malfunction of the sensor 206, or other software or hardware function associated with the test function of the testing device 100.

Power supplied to the various peripheral devices, including the RFID communications circuit 210, the light sensing circuit 1200, the touch screen LCD 110 and the microprocessor 1102 is controlled by the operating system. Thus, supply of power may be selectively switched off when the functions of the various devices are not needed for current operation of the testing device 100. The entire testing device 100 may also be placed into a “power down” state upon receiving a user command, or after a predetermined period of inactivity of the testing device 100. The power down state differs from the complete absence of power in that the date/time clock continues to operate and the RAM 1106 is maintained on power from the batteries 116 instead of the recovery battery backup, which activates upon complete power absence from the battery pack.

However, when the power down occurs, nearly all software activity ceases except for the processes required to monitor the state of the touch screen LCD 110. The user may “power up” the unit by touching the touch screen LCD 110. As previously mentioned, upon detection of the restoration of batteries 116 power after a total power loss, the software does not require the entry of date and time information as the recovery battery backup maintains this minimal function. In the present embodiment, the time period set for the testing device 100 to automatically power down based on a period of inactivity depends on which menu is displayed. The delay periods are preferably adjustable using the settings menu of step 1312.

In certain embodiments of this invention, test cartridge assembly 300 includes a heater or heating device that is mounted on PathOne (testing device 100) lid 104 such that the heater is in direct thermal contact with reservoir card 500 when lid 104 is closed. A slight preload between the heater and reservoir card 500 is typically provided by way of a foam or spring element. Heating may be accomplished with a polymer PTC heating element having a self-limiting capability, wherein the maximum temperature is limited to less than 40° C. The heating function is active when the lid is closed, and may be active at all times, if desired. Reservoir heating may occur within 15 minutes or within other predetermined time periods. In other embodiments, alternate heating systems, devices, and methodologies are used with testing device 100; therefore, the heating device described herein is not meant to be limiting.

In addition to the features and components described above, certain embodiments of this invention include systems, devices, and methods for verifying the proper functionality of the mechanical and electrical aspects of testing device 100 with regard to: (i) processing and mixing the test sample, biosensor, and various reagents involved in detecting a target or analyte of interest in a biological sample; and (ii) detection of the signal generated by the biosensor when reacting with the analyte or target of interest. Biosensor reagents and other reagents compatible with this invention are also disclosed in U.S. Pat. Nos. 9,023,640; 9,701,994; and 9,701,995, all of which are incorporated by reference herein, in their entirety for all purposes. More specifically, this invention includes a unique testing device function verification cartridge designed to interface with testing device 100, that is described in greater detail below.

With reference to FIG. 18A through FIG. 18H, an exemplary embodiment of function verification cartridge 1800 includes cover 1802, which is attached to enclosure 1804. Enclosure 1804 contains printed circuit board 1806, battery tape 1808, battery 1810, shuttle 1812, and spring 1814. RFID tag 1816 is attached to the bottom of function verification cartridge 100 (see FIG. 18C) as are first filter 1820, second filter 1822, gasket 1824, filter holder 1826, and gasket 1828. Track 1834, along which shuttle 1812 travels, is also located on the bottom of function verification cartridge 100. As best shown in FIG. 18E, USB port 1830 and optional programming/debugging port 1832 are located on one side of function verification cartridge 100. With reference to FIGS. 19A-19B, function verification cartridge 1800 is shown above testing device 1900 (FIG. 19A) and inserted into testing device 1900 (FIG. 19B). Testing device 1900, an exemplary embodiment of which is described in detail above as testing device 100, includes body 1902, hinged lid 1904, and test cavity 1906 into which function verification cartridge 1800 is inserted when in use.

Function verification cartridge 1800 is essentially a performance assessment tool that provides the user of testing device 100 (labeled interchangeably with reference numerals 1900 in FIG. 19A and FIG. 19B) with a high degree of confidence that testing device 100 is functioning within acceptable parameters, which have been predetermined prior to testing. In general terms, testing device 100 utilizes at least four basic aspects or features with regard to its functionality: (i) dispensing plunger displacement; (ii) dispensing plunger speed (both (i) and (ii) for mixing engineered biosensor cells with a test sample), (iii) reaction chamber temperature (for thawing and activating the engineered biosensor cells); and (iv) light sensitivity (for capturing the output of the engineered biosensor cells upon reacting with a target of interest). Function verification cartridge 1800 measures plunger displacement and speed directly by mechanically interacting with the moving components included in testing device 100. Reaction chamber temperature is measured directly through use of a temperature sensor included in function verification cartridge 1800 that essentially replicates the thermal pathway occurring between the reaction chamber heater and the engineered biosensor cells when testing device 100 is in actual use. Function verification cartridge 1800 also generates a calibrated light output that is specific to testing device 100. Accordingly, if function verification cartridge 1800 is in use and testing device 100 captures a light reading that is not within device specifications, a failure of testing device 100 will be communicated to the user of testing device 100.

In an exemplary embodiment, function verification cartridge 1800 communicates with testing device 100 through two primary methods: (i) radio-frequency identification (RFID) and (ii) light (e.g., visible light). Function verification cartridge 1800 includes a passive, unique, RFID tag that is read by testing device 100 upon insertion of the test cartridge. Tag recognition of function verification cartridge 1800 initiates performance testing of testing device 100. Visible light is used both as a calibration tool and an error reporting tool. As performance testing progresses, if function verification cartridge 1800 captures any performance errors (e.g., temperature or displacement out of range, incorrect plunger speed, etc.), the error is reported in the form of light pulses that are captured by sensor 206 in testing device 100 (i.e., the photomultiplier tube or PMT, as it is referred to herein). If the PMT is not functioning in testing device 100, operational errors will not be reported; however, because testing device 100 recognizes that it is in testing mode (RFID tag read), an error will nonetheless be logged by function verification cartridge 1800.

As described in FIG. 20, FIG. 21A and FIG. 21B, and FIG. 22A and FIG.22B and as stated above and below, function verification cartridge 1800 tests the functionality of the PathOne device (testing device 100) by determining injection accuracy (e.g., plunger travel distance measurement); and PMT functionality (e.g., basic operation, range testing). By way of example, injection accuracy includes factors such as critical dispensing locations including 3mm and 9 mm travel marks; and assessment within an estimated 0.1 mm (or potentially better pending factory function verification cartridge calibration). Determining PMT functionality may include 16X discrete, individually controlled LEDs (8-bit control over LED brightness; the generation of light in the (estimated) 40-160000 photon/s range. The range can be shifted up or down with hardware changes as needed and actual output must still be tested along with precision/accuracy.

Certain embodiments of function verification cartridge 1800 include the following general features and/or functional aspects. A first general feature includes PathOne (testing device 100) plunger 424 displacement measurement. This function measures the travel of fluid injecting plunger 424 in testing device 100 and confirms that plunger 424 is extending the correct distance during testing of the system. If the correct distance is not achieved, the appropriate quantity of engineered biosensor cells or other cells will not be injected into reaction chamber 404. This function is typically implemented using a linear potentiometer, although in alternate embodiments, the following methods are used: (i) optical distance sensing (laser/IR reflected light); (ii) ultrasonic distance sensing; (iii) capacitive distance sensing; (iv) inductive/eddy current distance sensing; and (v) limit or break beam switches. A second general feature includes the displacement rate measurement of plunger 424. This function measures the travel speed of fluid injection plunger 424 in testing device 100 and confirms that the speed is within specification. If the speed is out of specification, proper mixing of the engineered cells with the test sample may not occur or may not occur properly. This method is typically implemented with a microcontroller (MCU)-based timer, although in alternate embodiments, an external timer is used (e.g., real time clock IC, external oscillator, etc.). A third general feature includes measuring the temperature of the reservoir heater. This function measures the reservoir heater temperature achieved while under test conditions and is implemented using a temperature sensing diode, although other embodiments involve the use of a resistance thermometer (RTD), thermistor (NTC or PTC), thermocouple, or infrared device. A fourth general feature includes creating controlled light output. This function generates a calibrated light output of a quantity “known” by the PathOne (testing device 100); therefore, the device will recognize when the onboard light measuring hardware (e.g., photo-multiplier tube- PMT) is no longer functioning properly. This function is typically implemented using an LED and current-controlled LED driver, although other embodiments involve the use of an LED and current limiting resistor with feedback to MCU or an LED and current mirror. A fifth general feature includes wireless communication. This function identifies the POCC to the PathOne device (testing device 100) for the purpose of initiating the PathOne performance test. This function is typically implemented using a passive RFID tag, although alternate embodiments involve the use of Bluetooth, Wifi, LoRa, or other wireless communications systems.

Certain embodiments of function verification cartridge 1800 also include the following additional features. A first feature is a ˜200 mAh li-poly battery with fusing on both the charge and discharge sides of the battery. Multiple tests can be run before recharging is needed and a single charge can last several weeks when the system is in sleep mode. On-board battery charging is possible with a USB micro cable or other cable, with a 2-3-hour charge time (CC/CV). Device standalone charging functionality operates independently from MCU. Charging may be limited by battery temperature (e.g., battery will not charge if outside 0-50° C. range). Current-based charge termination (10 mA), is also provided. A second feature is a PathOne installation sense switch, wherein function verification cartridge 1800 recognizes when it has been installed in the PathOne device (testing device 100). A third feature is status indication, which may include: (i) a pulsing yellow LED when charging (USB cable connected); (ii) a green LED when the system is ready for testing (USB cable disconnected); (iii) a red LED when charging is needed (USB cable disconnected); and (iv) status LED shutdown when installed in the PathOne device or during sleep mode. A fourth feature is sleep mode, which occurs about one minute after charging is complete, the USB cable has been disconnected, or the function verification cartridge has been removed from the PathOne device (testing device 100). The system wakes up when a USB cable is connected or upon the depression of the PathOne installation sense switch. Certain embodiments of this invention include a user depressible switch. A fifth feature includes a PathOne (testing device 100) error indication, which may be communicated to the PMT through various blinks of an LED. If the PMT does not operate correctly, function verification cartridge 1800 cannot communicate to the PathOne (testing device 100), but this will be a known error on the PathOne side. Displacement distance (plunger 424) and time are evaluated, and errors are indicated within a predetermined period of time (50% duty cycle pulse). PMT functionality is evaluated based on predetermined ranges and errors are evaluated on the PathOne side.

FIG. 20 is a flowchart that illustrates a possible stepwise operation of an exemplary function verification cartridge 1800 from the perspective of the user of the disclosed system. In FIG. 20, FIG. 21A and FIG. 21B, and FIG. 22A and FIG. 22B and in this description, function verification cartridge 1800 is referred to as “POCC”, which is an abbreviation for “PathOne Confirmation Cartridge”. With reference to FIG. 20, the analysis from User Perspective 2000 starts at step 2010 with the POCC being connected to a charging source. At process step 2012, the user looks at the status indicator and determines that the LED is pulsing yellow at decision step 2014. If the LED is pulsing yellow at step 2014, the POCC is disconnected at process step 2016 and at decision step 2018, the LED will be determined to be either red or green. If the LED is red, additional charging will be required, and the POCC will be reconnected to the charger for a period of about one hour. If the LED is determined to be off at decision step 2022, the POCC is disconnected at process step 2024. If the LED is determined to be red or off at decision step 2026, a system error or determination that the POCC needs repair is made at stop 2028. If the LED is green at decision steps 2018 and 2026 the POCC is placed into the PathOne device at process step 2030. A determination that the RFID tag 1816 has been recognized as the POCC (an indication appears on the PathOne screen) occurs at decision step 2032. If RFID 1816 tag has not been recognized, a system error or determination that the POCC needs repair is made at stop 2028. If RFID 1816 has been recognized, the lid of testing device 100 is closed and the function verification test is executed at process step 2034. At decision step 2036, a determination is made regarding whether the PathOne device reports any errors. If no errors are reported, the POCC is reconnected to the charging cable at step 2038. If errors are reported and the POCC status LED is green at decision step 2042, an issue with the PathOne device is identified at process step 2040 and the error is reviewed on the PathOne screen. If the POCC status LED is not green at decision step 2042, a determination is made at process step 2044 that an issue may exist with the POCC or with the PathOne device itself. The PathOne device may also be retested with another POCC.

FIG. 21A and FIG. 21B are a flowchart that illustrates the stepwise operation of function verification cartridge 1800 (i.e., POCC) from the perspective of the function verification cartridge itself. The analysis from the POCC Perspective 2100 (function verification cartridge 1800) starts at step 2110 with a determination being made at decision step 2112 that the charging cable is connected. A determination that any existing charge is sufficient for testing is made at decision step 2114, and if the charge is sufficient, the status LED will display as solid green at process step 2116. A determination that charging is complete is made at decision step 2118. If charging is complete, the status LED is turned off at process step 2120. If charging is not complete, the status LED flashes yellow at process step 2122. If the existing charge is not sufficient for testing, that status LED will display as solid red at process step 2124 and the POCC is returned to the charger at process step 2126 (the test will not execute if the POCC is placed into the PathOne device in this state). A determination that the PathOne installation switch has been depressed is made at decision step 2128. If the installation switch has been depressed, the status LED will be off at process step 2130 and if the installation switch has not been depressed the status LED will displace as solid green (note: the LED times out after 10-20 s to save battery life). A determination that plunger 424 has reached “preliminary injection complete” position in a predetermined timeframe at (optional) decision step 2134 and if plunger 424 has not reached the desired position, the LED generates an error pulse train at process step 2136 (note: if shutter 236 has not opened at all, the error message will not be logged). If plunger 424 has not reached the desired position, a confirmation pulse is generated at process step 2138. A determination that plunger 424 is returning to the home position is made at decision step 2140. If plunger 42 is determined to not be returning to the home position, a determination that plunger 424 has reached a “primary injection complete” position in a predetermined timeframe is made at decision step 2142. If the determination is negative, the LED generates an error pulse train at process step 2144 (note: if shutter 236 has not opened at all, the error message will not be logged). If the determination is affirmative, a determination is then made at decision step 2146 that the temperature sensor has reached the correct temperature threshold. If the temperature sensor has not reached the correct temperature threshold, the LED generates an error pulse train at process step 2148 (note: if shutter 236 has not opened at all, the error message will not be logged). If the temperature sensor has reached the correct temperature threshold, a confirmation pulse is generated at process step 2150. A determination is again made at decision step 2152 that plunger 424 is returning home. If the determination is affirmative, the PathOne test is cancelled due to logged error at process step 2154. If the determination is negative, at (optional) process step 2156, a PMT dynamic range test commences (3x pulses, low end of operational range, 3x pulses, high end of operational range). A determination that the dynamic range test was completed before plunger movement resumed is then made at decision step 2158. If the determination is negative, the LED generates an error pulse train at process step 2160. If the answer is affirmative, a determination is then made that plunger 424 reached the “control injection complete” position in a predetermined timeframe at decision step 2162. If the determination is negative, the LED generates an error pulse train at process step 2164. If the determination is affirmative, a confirmation pulse is generated at process step 2166. At decision step 2169, a determination is made regarding plunger 424 returning home. If the answer is affirmative, a confirmation pulse is generated at process step 2170 (this indication is used to confirm closure of shutter 236). If the answer is negative, an error pulse train is generated at process step 2172 (this occurs as a continuous loop until the POCC is removed from the PathOne testing device 100. A determination that the POCC charge is sufficient for testing is made at decision step 2174 and if the answer is affirmative, the status LED will display as solid green at process step 2176. If the answer is negative, the status LED will display as solid red at decision step 2178. In either case, the process ends at step 2180.

FIG. 22A and FIG. 22B are a flowchart that illustrates the stepwise operation of function verification cartridge 1800 (i.e., POCC) from the perspective of testing device 100 (i.e., the PathOne testing device), in accordance with an exemplary embodiment of the present invention. The analysis from the PathOne Perspective 2200 (testing device 100) starts at step 2210 with a determination that the lid is open at decision step 2212. A determination is then made at decision step 2214 that the RFID Tag has been read. A determination is then made at decision step 2216 that the POCC tag has been read. If the determination is negative, the normal test run commences at step 2218. If the determination is affirmative, an advance to preliminary injection complete position occurs at process step 2220. A determination that a confirmation pulse has been captured is then made at decision step 2222. If the determination is negative, a determination that an error pulse has been captured is then made at decision step 2224. If the determination is negative, a shutter issue is assumed, and if the determination is affirmative, a rate or distance issue is assumed, and plunger 424 returns home at process step 2226. “Test complete” is then displayed on the error screen at step 2248. If the determination is made at decision step 2222 that a confirmation pulse has been captured, plunger 424 advances to the primary injection complete position at process step 2228. A determination is then again made at decision step 2230 as to whether a confirmation pulse has been captured. If the determination is negative, a determination that an error pulse has been captured is then made at decision step 2232. If the determination is negative, a shutter issue is assumed, and if the determination is affirmative, a rate or distance issue is assumed, and plunger 424 returns home at process step 2226. If the determination is made at decision step 2230 that a confirmation pulse has been captured, then at decision step 2234, a determination is made that both the low and high ends of the dynamic range test were captured. If the determination is negative, plunger 424 returns home at process step 2226. If the determination is affirmative, plunger 424 advances to the control injection complete position at process step 2236. A determination is then made at decision step 2238 that a confirmation pulse has been captured. If the determination is negative, a determination that an error pulse has been captured is then made at decision step 2240. If the determination is negative, a shutter issue is assumed, and if the determination is affirmative, a rate or distance issue is assumed, and plunger 424 returns home at process step 2226. If the determination that a confirmation pulse has been captured is positive, then the plunger returns home at process step 2242. A determination that an error pulse has been captured (shutter not closed) is made at decision step 2244, and if the determination is negative, the test is completed at step 2246. If the determination that an error pulse has been captured is affirmative, “Test complete” is then displayed on the error screen at step 2248.

While various embodiments in accordance with the principles disclosed herein have been described above, it should be understood that they have been presented by way of example only and not limitation. Thus, the breadth and scope of this disclosure should not be limited by any of the above-described exemplary embodiments but should be defined only in accordance with any claims and their equivalents issuing from this disclosure. Furthermore, the above advantages and features are provided in described embodiments but shall not limit the application of such issued claims to processes and structures accomplishing any or all of the above advantages.

Additionally, the section headings herein are provided for consistency with the suggestions under 37 C.F.R. 1.77 or otherwise to provide organizational purposes. These headings shall not limit or characterize the invention(s) set out in any claims that may issue from this disclosure. Specifically, and by way of example, a description of a technology in the “Background” is not to be construed as an admission that certain technology is prior art to any embodiment(s) described in this disclosure. Neither is the “Summary” to be considered as a specific characterization of the embodiment(s) set forth in issued claims. Furthermore, any reference in this disclosure to “invention” in the singular should not be used to argue that there is only a single point of novelty in this disclosure. Multiple embodiments may be set forth according to the limitations of the multiple claims issuing from this disclosure, and such claims accordingly define the embodiment(s), and their equivalents, that are protected thereby. In all instances, the scope of such claims shall be considered on their own merits in light of this disclosure but should not be constrained by the headings set forth and contained herein. 

What is claimed: 1) A system for conducting an assay that rapidly detects the presence of a target analyte in a biological sample, comprising: (a) a testing device, wherein the testing device includes a sensor for measuring a detectable signal that is generated upon the reaction of a biosensor reagent with a specific target analyte within a biological sample; (b) a reservoir card, wherein the reservoir card includes a biosensor reagent, wherein the biosensor reagent includes living, engineered biological cells, and wherein the reservoir card is configured to interface with a test cartridge base; (c) a test cartridge base, wherein the test cartridge base is configured to accept the reservoir card and to be placed within the testing device, wherein the test cartridge base further includes a reaction chamber that is adapted to receive both the biosensor reagent and the biological sample, and a fluid displacement mechanism that includes a dispensing plunger, and wherein actuation of the dispensing plunger displaces the biosensor reagent in the reservoir into the reaction chamber where the biosensor reagent is mixed with the biological sample; and (d) a function verification cartridge adapted to be received and recognized by the testing device, wherein the function verification cartridge is operative to confirm the proper functioning of the plunger and the sensor prior to conducting an assay for rapidly detecting the presence of the target analyte in the biological sample, and wherein confirmation of proper functioning is based on predetermined operational parameters. 2) The system of claim 1, wherein the detectable signal includes light, wherein the sensor includes a photomultiplier tube, and wherein the function verification cartridge is operative to determine sensitivity of the photomultiplier tube. 3) The system of claim 2, wherein the function verification cartridge generates a calibrated light output of a predetermined quantity that is recognized by the testing device as representing a proper amount of light output from the photomultiplier tube. 4) The system of claim 1, wherein the testing device further includes a heater for heating the reaction chamber, and wherein the function verification cartridge is operative to confirm proper functioning of the heater, and wherein confirmation of proper functioning is based on predetermined operational parameters. 5) The system of claim 4, wherein the proper functioning of the heater is determined by resistance thermometer; thermistor; thermocouple; infrared device; or combinations thereof. 6) The system of claim 1, wherein the function verification cartridge is operative to determine displacement of the dispensing plunger, and wherein displacement of the dispensing plunger is determined by linear potentiometer; optical distance sensing; ultrasonic distance sensing; capacitive distance sensing; inductive/eddy current distance sensing; limit or break beam switches; or combinations thereof. 7) The system of claim 1, wherein the function verification cartridge is operative to determine travel speed of the dispensing plunger, and wherein travel speed of the plunger is determined by a microcontroller-based timer; a real time clock; external oscillator; or combinations thereof. 8) The system of claim 1, wherein the function verification cartridge includes a radio-frequency identification tag that communicates with the testing device. 9) The system of claim 1, wherein the function verification cartridge communicates with the testing unit through visible light. 10) The system of claim 1, wherein upon recognition of the function verification cartridge by the testing device, the function verification cartridge immediately initiates performance testing of the testing device, and wherein errors detected by the function verification cartridge are reported in the form of light pulses that are captured by the sensor in the testing device. 11) A system for conducting an assay that rapidly detects the presence of a target analyte in a biological sample, comprising: (a) a portable testing device, wherein the portable testing device includes a sensor for measuring a detectable light signal that is generated upon the reaction of a biosensor reagent with a specific target analyte within a biological sample; (b) a reservoir card, wherein the reservoir card includes a biosensor reagent, wherein the biosensor reagent includes living, engineered biological cells, and wherein the reservoir card is configured to interface with a test cartridge base; (c) a test cartridge base, wherein the test cartridge base is configured to accept the reservoir card and to be placed within the portable testing device, wherein the test cartridge base further includes a reaction chamber that is adapted to receive both the biosensor reagent and the biological sample, and a fluid displacement mechanism that includes a dispensing plunger, and wherein actuation of the dispensing plunger displaces the biosensor reagent in the reservoir into the reaction chamber where the biosensor reagent is mixed with the biological sample; and (d) a function verification cartridge adapted to be received and recognized by the portable testing device, wherein the function verification cartridge is operative to determine displacement and travel speed of the dispensing plunger and functionality of the sensor prior to conducting an assay for rapidly detecting the presence of the target analyte in the biological sample. 12) The system of claim 11, wherein the sensor includes a photomultiplier tube, and wherein the function verification cartridge generates a calibrated light output of a predetermined quantity that is recognized by the testing device as representing a proper amount of light output from the photomultiplier tube. 13) The system of claim 11, wherein the testing device further includes a heater for heating the reaction chamber, wherein the function verification cartridge is operative to confirm proper functioning of the heater, and wherein the proper functioning of the heater is determined by resistance thermometer; thermistor; thermocouple; infrared device; or combinations thereof. 14) The system of claim 11, wherein the displacement of the dispensing plunger is determined by linear potentiometer; optical distance sensing; ultrasonic distance sensing; capacitive distance sensing; inductive/eddy current distance sensing; limit or break beam switches; or combinations thereof and wherein the travel speed of the plunger is determined by a microcontroller-based timer; a real time clock; external oscillator; or combinations thereof. 15) The system of claim 11, wherein the function verification cartridge communicates with the testing unit through radio-frequency identification, through visible light, or a combination thereof. 16) The system of claim 11, wherein upon recognition of the function verification cartridge by the testing device, the function verification cartridge immediately initiates performance testing of the testing device, and wherein errors detected by the function verification cartridge are reported in the form of light pulses that are captured by the sensor in the testing device. 17) A system for conducting an assay that rapidly detects the presence of a target analyte in a biological sample, comprising: (a) a portable testing device, wherein the portable testing device includes a photomultiplier tube for measuring a detectable light signal that is generated upon the reaction of a biosensor reagent with a specific target analyte within a biological sample; (b) a reservoir card, wherein the reservoir card includes a biosensor reagent, wherein the biosensor reagent includes living, engineered biological cells, and wherein the reservoir card is configured to interface with a test cartridge base; (c) a test cartridge base, wherein the test cartridge base is configured to accept the reservoir card and to be placed within the portable testing device, wherein the test cartridge base further includes a reaction chamber that is adapted to receive both the biosensor reagent and the biological sample, and a fluid displacement mechanism that includes a dispensing plunger, and wherein actuation of the dispensing plunger displaces the biosensor reagent in the reservoir into the reaction chamber where the biosensor reagent is mixed with the biological sample; (d) a function verification cartridge adapted to be received and recognized by the portable testing device, wherein the function verification cartridge is operative to determine displacement and travel speed of the dispensing plunger and functionality and sensitivity of the photomultiplier tube prior to conducting an assay for rapidly detecting the presence of the target analyte in the biological sample; and (e) a heater for heating the reaction chamber, wherein the function verification cartridge is further operative to confirm proper functioning of the heater based on predetermined operational parameters. 18) The system of claim 18, wherein the function verification cartridge generates a calibrated light output of a predetermined quantity that is recognized by the testing device as representing a proper amount of light output from the photomultiplier tube. 19) The system of claim 19, wherein the proper functioning of the heater is determined by resistance thermometer; thermistor; thermocouple; infrared device; or combinations thereof. 20) The system of claim 20, wherein the displacement of the dispensing plunger is determined by linear potentiometer; optical distance sensing; ultrasonic distance sensing; capacitive distance sensing; inductive/eddy current distance sensing; limit or break beam switches; or combinations thereof; and wherein the travel speed of the plunger is determined by a microcontroller-based timer; a real time clock; external oscillator; or combinations thereof. 